WO2008093275A2 - Event sharing restoration for photon counting detectors - Google Patents

Event sharing restoration for photon counting detectors Download PDF

Info

Publication number
WO2008093275A2
WO2008093275A2 PCT/IB2008/050294 IB2008050294W WO2008093275A2 WO 2008093275 A2 WO2008093275 A2 WO 2008093275A2 IB 2008050294 W IB2008050294 W IB 2008050294W WO 2008093275 A2 WO2008093275 A2 WO 2008093275A2
Authority
WO
WIPO (PCT)
Prior art keywords
coincidence
detector
pulse
detection data
correction
Prior art date
Application number
PCT/IB2008/050294
Other languages
French (fr)
Other versions
WO2008093275A3 (en
Inventor
Roland Proksa
Original Assignee
Koninklijke Philips Electronics N.V.
Philips Intellectual Property & Standards Gmbh
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 Koninklijke Philips Electronics N.V., Philips Intellectual Property & Standards Gmbh filed Critical Koninklijke Philips Electronics N.V.
Priority to CN200880003815.8A priority Critical patent/CN101600974B/en
Priority to US12/523,998 priority patent/US8050385B2/en
Publication of WO2008093275A2 publication Critical patent/WO2008093275A2/en
Publication of WO2008093275A3 publication Critical patent/WO2008093275A3/en

Links

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
    • G01T1/29—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
    • G01T1/2921—Static instruments for imaging the distribution of radioactivity in one or two dimensions; Radio-isotope cameras
    • G01T1/2928—Static instruments for imaging the distribution of radioactivity in one or two dimensions; Radio-isotope cameras using solid state detectors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/027—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis characterised by the use of a particular data acquisition trajectory, e.g. helical or spiral

Definitions

  • the invention relates to the field of tomographic imaging.
  • the invention relates to a detector unit for performing a coincidence detection and correction, an examination apparatus for examination of an object of interest, a method of examination of an object of interest, a computer-readable medium, a program element and a signal processing device.
  • Photon counting detectors with energy discrimination are a key component for future spectral computed tomography (CT) systems.
  • CT computed tomography
  • Current detector designs based on cadmium/zinc/tellurium (CZT) as primary converter are designed for detecting and counting incoming photons, which interact with the CZT, thereby generating an electron cloud. The generated electrons are accelerated towards an anode array, resulting in a pulse.
  • CZT cadmium/zinc/tellurium
  • the first is the so-called pulse sharing effect. If an X-ray photon hits the CZT somewhere between two anodes, the generated electrons might be shared between the two anodes. The electronic may interpret the signals as two independent events with shared energy. Another effect that causes a similar wrong interpretation may happen if the X-ray photon generates a so-called fluorescence photon. In such a case the energy of the X-ray photon is partly given to the fluorescence photon and the rest is deposed locally. The energy of the fluorescence photon is relatively high and there is high likelihood that it reaches a neighbour cell. Again, a single incoming X-ray photon may generate two signals with shared energy equivalents.
  • the likelihood of both effects may depend on the cell size. Larger cells may suffer less from both effects.
  • the invention provides a detector unit, an examination apparatus, a method of examination of an object of interest, a computer-readable medium, a program element and a signal processing device with the features according to the independent claims.
  • a detector unit for performing a coincidence detection and correction comprising a first detector cell adapted for detecting a first pulse resulting in first detection data and a second detector cell adapted for detecting a second pulse resulting in second detection data, and a coincidence detection and correction unit (CDC unit) coupled to the first and second detector cells and adapted for detecting a coincidence of the first and second pulses, wherein the coincidence detection and correction unit is further adapted for performing a correction of the first detection data, if a coincidence is detected.
  • the detector unit may comprise a plurality of detector cells which are adapted for detecting electric pulses resulting from incoming photons.
  • Each detector cell may be coupled to a respective electronic unit, which, in turn, does not only watch the electric pulses detected by the respective detector cell, but also the pulses detected by neighbouring detector cells.
  • the electronic unit detects a coincidence of two pulses which are detected by neighbouring cells, the detected data is corrected according to the coincidence.
  • Such a correction may be performed by not counting the event in one cell and counting the event with an energy level of ei+e 2 in the other cell (wherein ei is the energy detected in the first cell and e 2 is the energy detected in the second, neighbouring cell).
  • This may provide for a dedicated coincidence detection and correction and thus for a reduction of the effects of pulse sharing and fluorescence induced crosstalk.
  • the detection of the coincidence is performed on the basis of an analysis of the first and second detection data.
  • the characteristics of the underlying physical effects are analyzed.
  • the specific characteristics are that the two pulses of a pulse sharing event are detected at the same time and have a similar pulse shape but perhaps different amplitudes.
  • the respective set of energies for the fluorescence event may be analyzed.
  • the first detector cell is adapted for generating a first and a second measure corresponding to the first pulse, wherein the first measure corresponds to a first time of the first pulse and wherein the second measure corresponds to a first energy of the first pulse.
  • the second detector cell is adapted for generating a third and a fourth measure corresponding to the second pulse, wherein the third measure corresponds to a second time of the second pulse and wherein the fourth measure corresponds to a second energy of the second pulse.
  • the analysis is performed on the basis of the first, second, third and fourth measure.
  • the detection times and the energies of the pulses may be measured and compared with each other.
  • the coincidence detection and correction unit is parameterised by a set of thresholds.
  • the set of thresholds may comprise the allowed time window for pulse sharing, the allowed time window for fluorescence, the threshold for the similarity measure to detect pulse sharing and the maximal energy for X-ray photons.
  • the correction of the first detection data is performed on the basis of a priority assignment of coincidences.
  • the first pulse and the second pulse correspond to electromagnetic radiation impinging on the detector unit.
  • the detector unit may be adapted for detecting single photons.
  • the electromagnetic radiation is X-ray radiation.
  • the detector unit may be used in connection with an examination apparatus for medical applications, such as a computer tomography examination apparatus or a rotational X-ray apparatus.
  • the detector unit comprises a third detector cell adapted for detecting a third pulse, wherein the first, second and third detector cells have a shape such that a likelihood of a coincidence of the first and second pulses is bigger than a likelihood of a coincidence of the first and third pulses.
  • a cell, which has four neighbouring cells may not need four CDC- units for the four neighbour cells.
  • the number of CDC-units may be reduced to two for the neighbours at the larger sides of the detector cell.
  • an examination apparatus with a detector unit for examination of an object of interest and for performing a coincidence detection and correction
  • the detector unit comprises a first detector cell adapted for detecting a first pulse resulting in first detection data and a second detector cell adapted for detecting a second pulse resulting in second detection data, and a coincidence detection and correction unit coupled to the first and second detector cells and adapted for detecting a coincidence of the first and second pulses, wherein the coincidence detection and correction unit is further adapted for performing a correction of the first detection data, if a coincidence is detected.
  • the examination apparatus is configured as one of the group consisting of a material testing apparatus, a baggage inspection apparatus and a medical application apparatus.
  • the examination apparatus is adapted as one of a computed tomography apparatus and a rotational X-ray apparatus.
  • a method of examination of an object of interest in which a first pulse is detected by a first detector cell, resulting in first detection data, and in which a second pulse is detected by a second cell, resulting in second detection data. Furthermore, a coincidence of the first and second pulses is detected, for example by a coincidence detection and correction unit coupled to the first and second detector cells. Furthermore, a correction of the first detection data is performed, if a coincidence is detected.
  • a correction of the first detection data may be performed, but also a correction of the second detection data, or vice versa.
  • the form of the correction may depend on the quality of the detected coincidence event.
  • a computer-readable medium in which a computer program for examination of an object of interest is stored which, when being executed by a processor, causes the processor to carry out the above-mentioned method steps.
  • a program element for examination of an object of interest is provided, which, when being executed by a processor, causes the processor to carry out the above-mentioned method steps.
  • the method of examination of the object of interest may be embodied as the computer program, i.e. by software, or may be embodied using one or more special electronic optimization circuits, i.e. in hardware, or the method may be embodied in hybrid form, i.e. by means of software components and hardware components.
  • the program element according to an exemplary embodiment of the present invention is preferably loaded into working memories of a data processor.
  • the data processor may thus be equipped to carry out embodiments of the methods of the present invention.
  • the computer program may be written in any suitable programming language, such as, for example, C++ and may be stored on a computer-readable medium, such as a CD-ROM. Also, the computer program may be available from a network, such as the WorldWideWeb, from which it may be downloaded into image processing units or processors, or any suitable computers.
  • an image processing or signal processing device for examination of an object of interest comprising a memory for storing a data set of the object of interest, the data set comprising first detection data relating to a first pulse and second detection data relating to a second pulse, wherein the signal processing device is adapted for detecting a coincidence of the first and second pulses and performing a correction of the first detection data, if a coincidence is detected.
  • a detector unit may comprise a plurality of detector cells, wherein a coincidence detection and correction unit of a respective detector cell watches the signals detected at neighbouring cells. If there is a pulse at the same time in a neighbouring cell, the pulses are analyzed and a correction is applied to the data. The analysis of the pulses may be optimized with respect to the characteristics of the underlying physical effects.
  • Fig. 1 shows a simplified schematic representation of a CT examination apparatus according to an exemplary embodiment of the present invention.
  • Fig. 2 shows a simplified schematic representation of a CZT detector.
  • Fig. 3 shows a simplified schematic representation of a detector geometry according to an exemplary embodiment of the present invention.
  • Fig. 4 shows a simplified schematic representation of a detector geometry according to another exemplary embodiment of the present invention.
  • Fig. 5 shows a flow-chart of an exemplary method according to the present invention.
  • Fig. 6 shows an exemplary embodiment of a processing device according to the present invention, for executing an exemplary embodiment of a method in accordance with the present invention.
  • Fig. 1 shows an exemplary embodiment of a computer tomography scanner system according to the present invention.
  • the computer tomography apparatus 100 depicted in Fig. 1 is a cone-beam CT scanner. However, the invention may also be carried out with a fan-beam geometry. In order to generate a primary fan-beam, the aperture system 105 can be configured as a slit collimator.
  • the CT apparatus depicted in Fig. 1 comprises a gantry 101, which is rotatable around a rotational axis 102.
  • the gantry 101 is driven by means of a motor 103.
  • Reference numeral 104 designates a source of radiation such as an X-ray source, which, according to an aspect of the present invention, emits polychromatic or monochromatic radiation.
  • Reference numeral 105 designates an aperture system which forms the radiation beam emitted from the radiation source to a cone-shaped radiation beam 106.
  • the cone-beam 106 is directed such that it penetrates an object of interest 107 arranged in the centre of the gantry 101, i.e. in an examination region of the CT scanner, and impinges onto the detector 108.
  • the detector 108 is arranged on the gantry 101 opposite to the source of radiation 104, such that the surface of the detector 108 is covered by the cone-beam 106.
  • the detector 108 depicted in Fig. 1 comprises a plurality of detector elements 123 each capable of detecting X-rays which have been scattered by or passed through the obj ect of interest 107.
  • the detector 108 is described below in greater detail, with respect to Fig. 2.
  • the source of radiation 104, the aperture system 105 and the detector 108 are rotated along the gantry 101 in the direction indicated by an arrow 116.
  • the motor 103 is connected to a motor control unit 117, which is connected to a reconstruction unit 118 (which may also be denoted as a calculation of determination unit).
  • the object of interest 107 is a human being which is disposed on an operation table 119.
  • the operation table 119 displaces the human being 107 along a direction parallel to the rotational axis 102 of the gantry 101.
  • the heart 130 is scanned along a helical scan path.
  • the operation table 119 may also be stopped during the scans to thereby measure single slices. It should be noted that in all of the described cases it is also possible to perform a circular scan, where there is no displacement in a direction parallel to the rotational axis 102, but only the rotation of the gantry 101 around the rotational axis 102.
  • an electrocardiogram device 135 may be provided which measures an electrocardiogram of the heart 130 of the human being 107 while X-rays attenuated by passing the heart 130 are detected by detector 108. The data related to the measured electrocardiogram are transmitted to the reconstruction unit 118.
  • the detector 108 is connected to the reconstruction unit 118.
  • the reconstruction unit 118 receives the detection result, i.e. read-outs from the detector element 123 of the detector 108 and determines a scanning result on the basis of these read-outs. Furthermore, the reconstruction unit 118 communicates with the motor control unit 117 in order to coordinate the movement of the gantry 101 with motors 103 and 120 with the operation table 119.
  • the reconstruction unit 118 may be adapted for reconstructing an image from read-outs of the detector 108.
  • the reconstructed image generated by the reconstruction unit 118 may be output to a display (not shown in Fig. 1) via an interface 122.
  • the reconstruction unit 118 may be realized by a data processor to process read-outs from the detector element 123 of the detector 108.
  • the calculation unit may be connected to a loudspeaker 121 to automatically output an acoustic signal.
  • the measured data namely the cardiac computer tomography data and electrocardiogram data are processed by the reconstruction unit 118 which may be further controlled via a graphical user- interface 140.
  • This retrospective analysis may be based on helical cardiac cone-beam reconstruction scheme using retrospective ECG gating. It should be noted, however, that the present invention is not limited to the specific data acquisition and construction.
  • Fig. 2 shows a simplified schematic representation of a CZT detector 200, which may be implemented in a CT examination apparatus, such as detector 108 of Fig. 1.
  • the detector 200 comprises a substrate 208 and a cadmium/zinc/tellurium (CZT) layer 209. Furthermore, a cathode 207 and an anode array, comprising anodes or detector cells 201 , 202, 205 are provided.
  • CZT cadmium/zinc/tellurium
  • FIG. 3 shows a simplified schematic representation of a detector geometry.
  • the detector unit depicted in Fig. 3 comprises 9 detector cells, such as detector cells 201, 202.
  • the detector unit comprises twelve coincidence detection and correction units, i.e. CDC-units 203 and 301-311. it should be noted, that a detector unit according to the invention may comprise many more detector cells and CDC-units. As may be seen from Fig.
  • each detector cell has a CDC-unit which couples the cell to a neighbouring cell. Therefore, a coincidence detection is realized in such a way that the electronics of each detector cell watches the signals detected in the neighbouring cells. If there is a pulse at the same time in a neighbour cell, the pulses can be analyzed and a correction can be applied to the data.
  • the analysis of the pulses may be optimized with respect to the characteristics of the underlying physical effects. Such specific characteristics are, for example, that the two pulses of a pulse sharing event appear at the very same time and have a very similar pulse shape but perhaps different amplitudes. In fluorescence one may know very precisely the possible set of energies for the fluorescence event. As an example, if a CZT detector is used the fluorescence energies of cadmium and tellurium are known.
  • coincidence detection and correction may be realized with analogous or digital components (or a mixture thereof).
  • a description of the coincidence detection and correction is given below by means of an algorithmic specification independent of the hardware realization.
  • a respective coincidence detection and correction unit may be placed between every two neighbouring cells for which a coincidence is expected.
  • each detector cell generates two measures per incoming pulse. These measures include the time t of the event and the energy e of the event.
  • the CDC-unit comprises a measuring device for measuring the similarity of the pulse shape of the two neighbour cells.
  • the CDC-unit is parameterized by a set of thresholds.
  • T 1 i.e. the allowed time window for pulse sharing
  • T 2 i.e. the allowed time window for fluorescence
  • T s i.e. the threshold for the similarity measure to detect pulse sharing
  • T e i.e. the maximal energy for X-ray photons.
  • the parameter and threshold may be defined such that the advantage of coincidence detection and correction out performs the disadvantages by false-positive detection or indirect limitation of the count-rate capabilities.
  • priorities may be assigned to specific coincidences. These priorities may either be defined statically (e.g. a coincidence with the right neighbour has a higher priority than a coincidence with the left neighbour), dynamically (e.g. alternating priority, random choice) or systematically by calculating a likelihood measure for each coincidence and selecting the coincidence with the highest likelihood.
  • a conventional detector cell geometry may use squared electrodes, as depicted in Fig. 3.
  • Fig. 4 shows a schematic representation of a cell geometry according to another exemplary embodiment of the present invention.
  • the detector cells such as detector cells 201, 202, 204, are adapted in the form of rectangular electrodes having the same area as the squared electrodes of Fig. 3. Therefore, the likelihood of pulse sharing and fluorescence is reduced for the neighbours 404, 204 at the smaller sides of the detector cell 201.
  • the number of CDC-units 203, 402 may be reduced to two units for the neighbours 202, 403 at the larger sides. Consequently, a CDC-unit 401 may no longer be necessary.
  • Fig. 5 shows a flow-chart of a method according to an exemplary embodiment of the present invention.
  • the method starts at step 1 with the emission of electromagnetic radiation by a radiation source.
  • step 2 a first pulse which results in first detection data is detected by a first detector cell.
  • step 3 a second pulse is detected by a second detector cell, resulting in second detection data (step 3).
  • step 4 a coincidence of the first and second pulses is detected by the coincidence detection and correction unit connected to the first and second detector cells.
  • the measures of the two cells are corrected in step 5.
  • the correction consists of: a) not counting the event in one cell, and b) counting the event with an energy level of ei+e 2 in the other cell.
  • the question which cell has to be corrected according to which correction scheme may either be defined statically or dynamically (e.g. alternating or random).
  • Fig. 6 shows an exemplary embodiment of a data processing device 600 according to the present invention for executing an exemplary embodiment of a method in accordance with the present invention.
  • the data processing device 600 depicted in Fig. 6 comprises a central processing unit (CPU) or signal processor, such as an image processor 601 connected to a memory 602 for storing detection data acquired by a detector unit and representing an object of interest, such as a patient or an item of baggage.
  • the data processor or image processor 601 may be connected to a plurality of input/output network or diagnosis devices, such as a CT device.
  • the data processor 601 may furthermore be connected to a display device 603, for example, a computer monitor, for displaying information or an image computed or adapted in the data processor 601.
  • An operator or user may interact with the data processor 601 via a keyboard 604 and/or other output devices, which are not depicted in Fig. 6.
  • the bus system 605 it may also be possible to connect the signal processing and control processor 601 to, for example, a motion monitor, which monitors a motion of the object of interest.
  • a motion monitor which monitors a motion of the object of interest.
  • the motion sensor may be an exhalation sensor.
  • the motion sensor may be an electrocardiogram.
  • Exemplary embodiments of the invention may be sold as a software option to CT scanner console, imaging workstations or PACS workstations.

Landscapes

  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Molecular Biology (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Analysing Materials By The Use Of Radiation (AREA)
  • Apparatus For Radiation Diagnosis (AREA)
  • Investigating, Analyzing Materials By Fluorescence Or Luminescence (AREA)
  • Investigating Or Analysing Biological Materials (AREA)
  • Measurement Of Radiation (AREA)

Abstract

Photon counting detectors may suffer from pulse sharing effects and fluorescence photon generation, which may lead to a degradation of the measured signals. According to an exemplary embodiment of the present invention, a detector unit is provided which is adapted for performing a coincidence detection and correction by comparing detection events of neighbouring cells, thereby providing for a coincidence identification followed by an individual coincidence correction. In order to reduce the number of coincidence detection and corresponding units per detector unit, a specific detector cell geometry may be applied.

Description

Event sharing restoration for photon counting detectors
The invention relates to the field of tomographic imaging. In particular, the invention relates to a detector unit for performing a coincidence detection and correction, an examination apparatus for examination of an object of interest, a method of examination of an object of interest, a computer-readable medium, a program element and a signal processing device.
Photon counting detectors with energy discrimination are a key component for future spectral computed tomography (CT) systems. Current detector designs based on cadmium/zinc/tellurium (CZT) as primary converter are designed for detecting and counting incoming photons, which interact with the CZT, thereby generating an electron cloud. The generated electrons are accelerated towards an anode array, resulting in a pulse.
There are two well-known effects that cause a degradation of the measured signals. The first is the so-called pulse sharing effect. If an X-ray photon hits the CZT somewhere between two anodes, the generated electrons might be shared between the two anodes. The electronic may interpret the signals as two independent events with shared energy. Another effect that causes a similar wrong interpretation may happen if the X-ray photon generates a so-called fluorescence photon. In such a case the energy of the X-ray photon is partly given to the fluorescence photon and the rest is deposed locally. The energy of the fluorescence photon is relatively high and there is high likelihood that it reaches a neighbour cell. Again, a single incoming X-ray photon may generate two signals with shared energy equivalents.
The likelihood of both effects may depend on the cell size. Larger cells may suffer less from both effects.
However, another severe challenge is to reach high count-rates. High count- rates may be realized with small cells, because the count workload is divided over more small cells with lower individual count-rate requirements. A compromise has to be found between these two competing requirements.
It would be desirable to have a reduced degradation of measured signals for a photo counting detector. The invention provides a detector unit, an examination apparatus, a method of examination of an object of interest, a computer-readable medium, a program element and a signal processing device with the features according to the independent claims.
It should be noted that the following described exemplary embodiments of the invention apply also for the method of examination of the object of interest, for the computer- readable medium, for the program element and for the signal processing device.
According to a first aspect of the present invention, a detector unit for performing a coincidence detection and correction (CDC) is provided, the detector unit comprising a first detector cell adapted for detecting a first pulse resulting in first detection data and a second detector cell adapted for detecting a second pulse resulting in second detection data, and a coincidence detection and correction unit (CDC unit) coupled to the first and second detector cells and adapted for detecting a coincidence of the first and second pulses, wherein the coincidence detection and correction unit is further adapted for performing a correction of the first detection data, if a coincidence is detected. In other words, the detector unit may comprise a plurality of detector cells which are adapted for detecting electric pulses resulting from incoming photons. Each detector cell may be coupled to a respective electronic unit, which, in turn, does not only watch the electric pulses detected by the respective detector cell, but also the pulses detected by neighbouring detector cells. In case the electronic unit detects a coincidence of two pulses which are detected by neighbouring cells, the detected data is corrected according to the coincidence. Such a correction may be performed by not counting the event in one cell and counting the event with an energy level of ei+e2 in the other cell (wherein ei is the energy detected in the first cell and e2 is the energy detected in the second, neighbouring cell).
This may provide for a dedicated coincidence detection and correction and thus for a reduction of the effects of pulse sharing and fluorescence induced crosstalk.
According to another exemplary embodiment of the present invention, the detection of the coincidence is performed on the basis of an analysis of the first and second detection data.
For example, according to this exemplary embodiment, the characteristics of the underlying physical effects are analyzed. The specific characteristics are that the two pulses of a pulse sharing event are detected at the same time and have a similar pulse shape but perhaps different amplitudes. For fluorescence, the respective set of energies for the fluorescence event may be analyzed.
This may provide for an exact coincidence detection. According to another exemplary embodiment of the present invention, the first detector cell is adapted for generating a first and a second measure corresponding to the first pulse, wherein the first measure corresponds to a first time of the first pulse and wherein the second measure corresponds to a first energy of the first pulse. Furthermore, the second detector cell is adapted for generating a third and a fourth measure corresponding to the second pulse, wherein the third measure corresponds to a second time of the second pulse and wherein the fourth measure corresponds to a second energy of the second pulse. The analysis is performed on the basis of the first, second, third and fourth measure.
Thus, for each pair of pulse detection events (each event being detected at one detector cell) the detection times and the energies of the pulses may be measured and compared with each other.
This may provide for an exact determination, whether a pulse sharing effect or a fluorescence photon generation has occurred.
According to another exemplary embodiment of the present invention, the coincidence detection and correction unit is parameterised by a set of thresholds.
For example, the set of thresholds may comprise the allowed time window for pulse sharing, the allowed time window for fluorescence, the threshold for the similarity measure to detect pulse sharing and the maximal energy for X-ray photons.
Furthermore, according to another exemplary embodiment of the present invention, the correction of the first detection data is performed on the basis of a priority assignment of coincidences.
These priorities may either be defined statically, dynamically or systematically by calculating a likelihood measure for each coincidence and selecting the coincidence with the highest likelihood. According to another exemplary embodiment of the present invention, the first pulse and the second pulse correspond to electromagnetic radiation impinging on the detector unit.
In other words, the detector unit may be adapted for detecting single photons.
According to another exemplary embodiment of the present invention, the electromagnetic radiation is X-ray radiation. Furthermore, the detector unit may be used in connection with an examination apparatus for medical applications, such as a computer tomography examination apparatus or a rotational X-ray apparatus.
Furthermore, according to another exemplary embodiment of the present invention, the detector unit comprises a third detector cell adapted for detecting a third pulse, wherein the first, second and third detector cells have a shape such that a likelihood of a coincidence of the first and second pulses is bigger than a likelihood of a coincidence of the first and third pulses.
Therefore, a cell, which has four neighbouring cells may not need four CDC- units for the four neighbour cells. The number of CDC-units may be reduced to two for the neighbours at the larger sides of the detector cell.
Furthermore, according to another exemplary embodiment of the present invention, an examination apparatus with a detector unit for examination of an object of interest and for performing a coincidence detection and correction is provided, wherein the detector unit comprises a first detector cell adapted for detecting a first pulse resulting in first detection data and a second detector cell adapted for detecting a second pulse resulting in second detection data, and a coincidence detection and correction unit coupled to the first and second detector cells and adapted for detecting a coincidence of the first and second pulses, wherein the coincidence detection and correction unit is further adapted for performing a correction of the first detection data, if a coincidence is detected.
This may provide for an examination apparatus which provides a reduced degradation of measured signals.
According to another exemplary embodiment of the present invention, the examination apparatus is configured as one of the group consisting of a material testing apparatus, a baggage inspection apparatus and a medical application apparatus.
Furthermore, according to another exemplary embodiment of the present invention, the examination apparatus is adapted as one of a computed tomography apparatus and a rotational X-ray apparatus.
According to another exemplary embodiment of the present invention, a method of examination of an object of interest is provided, in which a first pulse is detected by a first detector cell, resulting in first detection data, and in which a second pulse is detected by a second cell, resulting in second detection data. Furthermore, a coincidence of the first and second pulses is detected, for example by a coincidence detection and correction unit coupled to the first and second detector cells. Furthermore, a correction of the first detection data is performed, if a coincidence is detected.
It should be noted in this context, that not only a correction of the first detection data may be performed, but also a correction of the second detection data, or vice versa. The form of the correction may depend on the quality of the detected coincidence event. According to another exemplary embodiment of the present invention, a computer-readable medium is provided, in which a computer program for examination of an object of interest is stored which, when being executed by a processor, causes the processor to carry out the above-mentioned method steps. Furthermore, according to another exemplary embodiment of the present invention, a program element for examination of an object of interest is provided, which, when being executed by a processor, causes the processor to carry out the above-mentioned method steps.
Both skilled in the art will readily appreciate that the method of examination of the object of interest may be embodied as the computer program, i.e. by software, or may be embodied using one or more special electronic optimization circuits, i.e. in hardware, or the method may be embodied in hybrid form, i.e. by means of software components and hardware components.
The program element according to an exemplary embodiment of the present invention is preferably loaded into working memories of a data processor. The data processor may thus be equipped to carry out embodiments of the methods of the present invention. The computer program may be written in any suitable programming language, such as, for example, C++ and may be stored on a computer-readable medium, such as a CD-ROM. Also, the computer program may be available from a network, such as the WorldWideWeb, from which it may be downloaded into image processing units or processors, or any suitable computers.
Furthermore, according to another exemplary embodiment of the present invention, an image processing or signal processing device for examination of an object of interest is provided, the signal processing device comprising a memory for storing a data set of the object of interest, the data set comprising first detection data relating to a first pulse and second detection data relating to a second pulse, wherein the signal processing device is adapted for detecting a coincidence of the first and second pulses and performing a correction of the first detection data, if a coincidence is detected.
It may be seen as the gist of an exemplary embodiment of the present invention that a dedicated coincidence detection and correction method is used to reduce the effects of pulse sharing and fluorescence induced crosstalk. A detector unit according to an exemplary embodiment of the present invention may comprise a plurality of detector cells, wherein a coincidence detection and correction unit of a respective detector cell watches the signals detected at neighbouring cells. If there is a pulse at the same time in a neighbouring cell, the pulses are analyzed and a correction is applied to the data. The analysis of the pulses may be optimized with respect to the characteristics of the underlying physical effects.
These and other aspects of the present invention will become apparent from and elucidated with reference to the embodiments described hereinafter. Exemplary embodiments of the present invention will be described in the following, with reference to following drawings.
Fig. 1 shows a simplified schematic representation of a CT examination apparatus according to an exemplary embodiment of the present invention.
Fig. 2 shows a simplified schematic representation of a CZT detector. Fig. 3 shows a simplified schematic representation of a detector geometry according to an exemplary embodiment of the present invention.
Fig. 4 shows a simplified schematic representation of a detector geometry according to another exemplary embodiment of the present invention.
Fig. 5 shows a flow-chart of an exemplary method according to the present invention.
Fig. 6 shows an exemplary embodiment of a processing device according to the present invention, for executing an exemplary embodiment of a method in accordance with the present invention.
The illustration in the drawings is schematic. In different drawings, similar or identical elements are provided with the same reference numerals.
Fig. 1 shows an exemplary embodiment of a computer tomography scanner system according to the present invention.
The computer tomography apparatus 100 depicted in Fig. 1 is a cone-beam CT scanner. However, the invention may also be carried out with a fan-beam geometry. In order to generate a primary fan-beam, the aperture system 105 can be configured as a slit collimator.
The CT apparatus depicted in Fig. 1 comprises a gantry 101, which is rotatable around a rotational axis 102. The gantry 101 is driven by means of a motor 103. Reference numeral 104 designates a source of radiation such as an X-ray source, which, according to an aspect of the present invention, emits polychromatic or monochromatic radiation.
Reference numeral 105 designates an aperture system which forms the radiation beam emitted from the radiation source to a cone-shaped radiation beam 106. The cone-beam 106 is directed such that it penetrates an object of interest 107 arranged in the centre of the gantry 101, i.e. in an examination region of the CT scanner, and impinges onto the detector 108. As may be taken from Fig. 1, the detector 108 is arranged on the gantry 101 opposite to the source of radiation 104, such that the surface of the detector 108 is covered by the cone-beam 106. The detector 108 depicted in Fig. 1 comprises a plurality of detector elements 123 each capable of detecting X-rays which have been scattered by or passed through the obj ect of interest 107.
The detector 108 is described below in greater detail, with respect to Fig. 2.
During scanning of the object of interest 107, the source of radiation 104, the aperture system 105 and the detector 108 are rotated along the gantry 101 in the direction indicated by an arrow 116. For rotation of the gantry 101 with the source of radiation 104, the aperture system 105 and the detector 108, the motor 103 is connected to a motor control unit 117, which is connected to a reconstruction unit 118 (which may also be denoted as a calculation of determination unit).
In Fig. 1, the object of interest 107 is a human being which is disposed on an operation table 119. During the scan of, e.g., the heart 130 of the human being 107, while the gantry 101 rotates around the human being 107, the operation table 119 displaces the human being 107 along a direction parallel to the rotational axis 102 of the gantry 101. By this, the heart 130 is scanned along a helical scan path. The operation table 119 may also be stopped during the scans to thereby measure single slices. It should be noted that in all of the described cases it is also possible to perform a circular scan, where there is no displacement in a direction parallel to the rotational axis 102, but only the rotation of the gantry 101 around the rotational axis 102.
Moreover, an electrocardiogram device 135 may be provided which measures an electrocardiogram of the heart 130 of the human being 107 while X-rays attenuated by passing the heart 130 are detected by detector 108. The data related to the measured electrocardiogram are transmitted to the reconstruction unit 118.
The detector 108 is connected to the reconstruction unit 118. The reconstruction unit 118 receives the detection result, i.e. read-outs from the detector element 123 of the detector 108 and determines a scanning result on the basis of these read-outs. Furthermore, the reconstruction unit 118 communicates with the motor control unit 117 in order to coordinate the movement of the gantry 101 with motors 103 and 120 with the operation table 119.
The reconstruction unit 118 may be adapted for reconstructing an image from read-outs of the detector 108. The reconstructed image generated by the reconstruction unit 118 may be output to a display (not shown in Fig. 1) via an interface 122. The reconstruction unit 118 may be realized by a data processor to process read-outs from the detector element 123 of the detector 108.
Furthermore, as may be taken from Fig. 1, the calculation unit may be connected to a loudspeaker 121 to automatically output an acoustic signal. The measured data, namely the cardiac computer tomography data and electrocardiogram data are processed by the reconstruction unit 118 which may be further controlled via a graphical user- interface 140. This retrospective analysis may be based on helical cardiac cone-beam reconstruction scheme using retrospective ECG gating. It should be noted, however, that the present invention is not limited to the specific data acquisition and construction.
Fig. 2 shows a simplified schematic representation of a CZT detector 200, which may be implemented in a CT examination apparatus, such as detector 108 of Fig. 1.
The detector 200 comprises a substrate 208 and a cadmium/zinc/tellurium (CZT) layer 209. Furthermore, a cathode 207 and an anode array, comprising anodes or detector cells 201 , 202, 205 are provided.
Incoming photons 206 interact with the CZT 209 and generate an electron cloud. A strong electrical field between the top layer 207 and the bottom layer 208 accelerate this cloud towards the lower electrodes 201, 202, 205. The related pulse is detected and counted. The pulse height may allow the detection of the energy of the photon. Fig. 3 shows a simplified schematic representation of a detector geometry. The detector unit depicted in Fig. 3 comprises 9 detector cells, such as detector cells 201, 202. Furthermore, the detector unit comprises twelve coincidence detection and correction units, i.e. CDC-units 203 and 301-311. it should be noted, that a detector unit according to the invention may comprise many more detector cells and CDC-units. As may be seen from Fig. 3, each detector cell has a CDC-unit which couples the cell to a neighbouring cell. Therefore, a coincidence detection is realized in such a way that the electronics of each detector cell watches the signals detected in the neighbouring cells. If there is a pulse at the same time in a neighbour cell, the pulses can be analyzed and a correction can be applied to the data. The analysis of the pulses may be optimized with respect to the characteristics of the underlying physical effects. Such specific characteristics are, for example, that the two pulses of a pulse sharing event appear at the very same time and have a very similar pulse shape but perhaps different amplitudes. In fluorescence one may know very precisely the possible set of energies for the fluorescence event. As an example, if a CZT detector is used the fluorescence energies of cadmium and tellurium are known.
It should be noted that the coincidence detection and correction according to the invention may be realized with analogous or digital components (or a mixture thereof). A description of the coincidence detection and correction is given below by means of an algorithmic specification independent of the hardware realization. A respective coincidence detection and correction unit may be placed between every two neighbouring cells for which a coincidence is expected. For example, each detector cell generates two measures per incoming pulse. These measures include the time t of the event and the energy e of the event. Furthermore, the CDC-unit comprises a measuring device for measuring the similarity of the pulse shape of the two neighbour cells. In addition to the measures (tls t2, ei, e2) the CDC-unit is parameterized by a set of thresholds.
Four exemplary thresholds are:
T1, i.e. the allowed time window for pulse sharing, T2, i.e. the allowed time window for fluorescence, Ts, i.e. the threshold for the similarity measure to detect pulse sharing, and Te, i.e. the maximal energy for X-ray photons.
It may happen that two individual X-ray photons hit two neighbouring cells at about the same time. In this case care may have to be taken not to treat these events as pulse sharing or fluorescence. The parameter and threshold may be defined such that the advantage of coincidence detection and correction out performs the disadvantages by false-positive detection or indirect limitation of the count-rate capabilities.
In case a cell detects coincidences with more than one neighbour, priorities may be assigned to specific coincidences. These priorities may either be defined statically (e.g. a coincidence with the right neighbour has a higher priority than a coincidence with the left neighbour), dynamically (e.g. alternating priority, random choice) or systematically by calculating a likelihood measure for each coincidence and selecting the coincidence with the highest likelihood.
In order to minimize the effort for building and arranging the CDC-units by keeping them simple and by minimizing the number of CDC-units, optimized cell geometries may be implemented. A conventional detector cell geometry may use squared electrodes, as depicted in Fig. 3.
Fig. 4 shows a schematic representation of a cell geometry according to another exemplary embodiment of the present invention. Here, the detector cells, such as detector cells 201, 202, 204, are adapted in the form of rectangular electrodes having the same area as the squared electrodes of Fig. 3. Therefore, the likelihood of pulse sharing and fluorescence is reduced for the neighbours 404, 204 at the smaller sides of the detector cell 201. In such a design, the number of CDC-units 203, 402 may be reduced to two units for the neighbours 202, 403 at the larger sides. Consequently, a CDC-unit 401 may no longer be necessary.
It should be noted that the proposed CDC scheme may also be applied to other geometries than those shown with respect to Figs. 3 and 4.
Fig. 5 shows a flow-chart of a method according to an exemplary embodiment of the present invention. The method starts at step 1 with the emission of electromagnetic radiation by a radiation source. Then, in step 2, a first pulse which results in first detection data is detected by a first detector cell. More or less at the same time, a second pulse is detected by a second detector cell, resulting in second detection data (step 3). Then, in step 4, a coincidence of the first and second pulses is detected by the coincidence detection and correction unit connected to the first and second detector cells. If the similarity measure of the pulses exceeds a threshold (Ts) and the absolute difference of the pulse times (tls t2) is lower than a threshold (Ti) and the sum of the energy of the pulses (el s e2) does not exceed a threshold (Te) than pulse sharing is assumed.
If the absolute difference of the pulse times (tl s t2) is lower than a threshold (T2) and ei or e2 corresponds to one of the assumed fluorescence energy levels and the sum of the energy of the pulses (el s e2) does not exceed a threshold (Te) then fluorescence is assumed.
If a coincidence is detected (either pulse sharing or fluorescence) and the coincidence has the highest priority, the measures of the two cells are corrected in step 5. The correction consists of: a) not counting the event in one cell, and b) counting the event with an energy level of ei+e2 in the other cell.
The question which cell has to be corrected according to which correction scheme may either be defined statically or dynamically (e.g. alternating or random).
Fig. 6 shows an exemplary embodiment of a data processing device 600 according to the present invention for executing an exemplary embodiment of a method in accordance with the present invention.
The data processing device 600 depicted in Fig. 6 comprises a central processing unit (CPU) or signal processor, such as an image processor 601 connected to a memory 602 for storing detection data acquired by a detector unit and representing an object of interest, such as a patient or an item of baggage. The data processor or image processor 601 may be connected to a plurality of input/output network or diagnosis devices, such as a CT device. The data processor 601 may furthermore be connected to a display device 603, for example, a computer monitor, for displaying information or an image computed or adapted in the data processor 601. An operator or user may interact with the data processor 601 via a keyboard 604 and/or other output devices, which are not depicted in Fig. 6.
Furthermore, via the bus system 605, it may also be possible to connect the signal processing and control processor 601 to, for example, a motion monitor, which monitors a motion of the object of interest. In case, for example, a lung of a patient is imaged, the motion sensor may be an exhalation sensor. In case the heart is imaged, the motion sensor may be an electrocardiogram.
Exemplary embodiments of the invention may be sold as a software option to CT scanner console, imaging workstations or PACS workstations.
It should be noted that the term "comprising" does not exclude other elements or steps and the "a" or "an" does not exclude a plurality. Also elements described in association with different embodiments may be combined.
It should also be noted that reference signs in the claims shall not be construed as limiting the scope of the claims.

Claims

CLAIMS:
1. Detector unit (200) for performing a coincidence detection and correction, the detector unit (200) comprising: a first detector cell (201) adapted for detecting a first pulse resulting in first detection data and a second detector cell (202) adapted for detecting a second pulse resulting in second detection data; and a coincidence detection and correction unit (203) coupled to the first and second detector cells and adapted for detecting a coincidence of the first and second pulses; wherein the coincidence detection and correction unit (203) is further adapted for performing a correction of the first detection data, if a coincidence is detected.
2. The detector unit (200) of claim 1 , wherein the detection of the coincidence is performed on the basis of an analysis of the first and second detection data.
3 /The detector unit (200) of claim 2, wherein the first detector cell (201) is adapted for generating a first measure and a second measure corresponding to the first pulse; wherein the first measure corresponds to a first time of the first pulse and wherein the second measure corresponds to a first energy of the first pulse; wherein the second detector cell (202) is adapted for generating a third measure and a fourth measure corresponding to the second pulse; wherein the third measure corresponds to a second time of the second pulse and wherein the fourth measure corresponds to a second energy of the second pulse; wherein the analysis is performed on the basis of the first, second, third and fourth measure.
4. The detector unit (200) of claim 2, wherein the analysis is adapted for determining whether a pulse sharing event or a fluorescence photon generation event has occurred.
5. The detector unit (200) of claim 1 , wherein the coincidence detection and correction unit (203) is parameterised by a set of thresholds; and wherein the correction of the first detection data is performed on the basis of the parameterisation.
6. The detector unit (200) of claim 1 , wherein the correction of the first detection data is performed on the basis of a priority assignment of coincidences.
7. The detector unit (200) of claim 6, wherein the priority assignment is performed on the basis of a likelihood measure for each coincidence and a selection of a coincidence with the highest likelihood.
8. The detector unit (200) of claim 1 , wherein the first pulse and the second pulse correspond to electromagnetic radiation impinging on the detector unit.
9. The detector unit (200) of claim 8, wherein the electromagnetic radiation is x-ray radiation.
10. The detector unit (200) of claim 1 , wherein the detector unit (200) is adapted for a computed tomography examination apparatus.
11. The detector unit (200) of claim 1 , further comprising a third detector cell (204) adapted for detecting a third pulse; wherein the first, second and third detector cells (201, 202, 204) have a shape such that a likelihood of a coincidence of the first and second pulses is bigger than a likelihood of a coincidence of the first and third pulses.
12. Examination apparatus (100) with a detector unit (200) for examination of an object of interest (107) and for performing a coincidence detection and correction, the detector unit comprising: a first detector cell (201) adapted for detecting a first pulse resulting in first detection data and a second detector cell (202) adapted for detecting a second pulse resulting in second detection data; and a coincidence detection and correction unit (203) coupled to the first and second detector cells and adapted for detecting a coincidence of the first and second pulses; wherein the coincidence detection and correction unit (203) is further adapted for performing a correction of the first detection data, if a coincidence is detected.
13. The examination apparatus (100) of claim 12, the examination apparatus (100) being configured as one of the group consisting of a material testing apparatus, a baggage inspection apparatus, a medical application apparatus and a micro CT system.
14. The examination apparatus (100) of claim 12, the examination apparatus (100) being adapted as one of a computed tomography apparatus and a rotational X-ray apparatus.
15. A method of examination of an object of interest (107) with an examination apparatus (100), method comprising the steps of: detecting, by a first detector cell (201), a first pulse resulting in first detection data; detecting, by a second detector cell (202), a second pulse resulting in second detection data; detecting a coincidence of the first and second pulses; performing a correction of the first detection data, if a coincidence is detected.
16. A computer-readable medium (602), in which a computer program for examination of an object of interest is stored which, when executed by a processor (601), causes the processor to carry out the steps of: detecting, by a first detector cell (201), a first pulse resulting in first detection data; detecting, by a second detector cell (202), a second pulse resulting in second detection data; detecting a coincidence of the first and second pulses; performing a correction of the first detection data, if a coincidence is detected.
17. A program element for examination of an object of interest, which, when being executed by a processor (601), causes the processor to carry out the steps of: detecting, by a first detector cell (201), a first pulse resulting in first detection data; detecting, by a second detector cell (202), a second pulse resulting in second detection data; detecting a coincidence of the first and second pulses; performing a correction of the first detection data, if a coincidence is detected.
18. A signal processing device for examination of an object of interest (107), the signal processing device comprising: a memory for storing a data set of the object of interest (107), the data set comprising first detection data relating to a first pulse and second detection data relating to a second pulse; wherein the signal processing device is adapted for: detecting a coincidence of the first and second pulses; performing a correction of the first detection data, if a coincidence is detected.
PCT/IB2008/050294 2007-02-01 2008-01-28 Event sharing restoration for photon counting detectors WO2008093275A2 (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
CN200880003815.8A CN101600974B (en) 2007-02-01 2008-01-28 Event sharing restoration for photon counting detectors
US12/523,998 US8050385B2 (en) 2007-02-01 2008-01-28 Event sharing restoration for photon counting detectors

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
EP07101572 2007-02-01
EP07101572.1 2007-02-01

Publications (2)

Publication Number Publication Date
WO2008093275A2 true WO2008093275A2 (en) 2008-08-07
WO2008093275A3 WO2008093275A3 (en) 2008-11-06

Family

ID=39666223

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/IB2008/050294 WO2008093275A2 (en) 2007-02-01 2008-01-28 Event sharing restoration for photon counting detectors

Country Status (3)

Country Link
US (1) US8050385B2 (en)
CN (1) CN101600974B (en)
WO (1) WO2008093275A2 (en)

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20130294573A1 (en) * 2008-11-26 2013-11-07 Analogic Corporation Method of and apparatus for continuous wave tomosynthesis using photon counting
EP2730948A4 (en) * 2011-07-07 2015-04-08 Toshiba Kk Photon counting image detector, x-ray diagnosis apparatus, and x-ray computerized tomography apparatus
WO2018133087A1 (en) * 2017-01-23 2018-07-26 Shenzhen Xpectvision Technology Co., Ltd. X-ray detectors capable of identifying and managing charge sharing

Families Citing this family (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102011080077A1 (en) * 2011-07-29 2013-01-31 Siemens Aktiengesellschaft Method for detecting the true coincidence of two charge pulses on adjacent pixel elements, X-ray detector and X-ray image acquisition device
US8488854B2 (en) * 2011-12-07 2013-07-16 Ge Medical Systems Israel, Ltd. System and apparatus for classifying x-ray energy into discrete levels
EP3281039B1 (en) 2015-04-07 2020-03-11 Shenzhen Xpectvision Technology Co., Ltd. Semiconductor x-ray detector
CN107533146B (en) 2015-04-07 2019-06-18 深圳帧观德芯科技有限公司 Semiconductor X-Ray detector
US9915741B2 (en) 2015-04-07 2018-03-13 Shenzhen Xpectvision Technology Co., Ltd. Method of making semiconductor X-ray detectors
WO2016197338A1 (en) * 2015-06-10 2016-12-15 Shenzhen Xpectvision Technology Co.,Ltd. A detector for x-ray fluorescence
CN107710021B (en) 2015-07-09 2019-09-27 深圳帧观德芯科技有限公司 The method for making Semiconductor X-Ray detector
EP3341756A4 (en) 2015-08-27 2019-05-22 Shenzhen Xpectvision Technology Co., Ltd. X-ray imaging with a detector capable of resolving photon energy
CN107923987B (en) 2015-09-08 2020-05-15 深圳帧观德芯科技有限公司 Method for producing an X-ray detector
JP6700737B2 (en) * 2015-11-20 2020-05-27 キヤノン株式会社 Radiation imaging system, signal processing device, and signal processing method for radiation image
DE102016208320B3 (en) 2016-05-13 2017-03-09 Bruker Axs Gmbh Device for sorting materials, in particular scrap particles, by means of X-ray fluorescence
US10162066B2 (en) 2017-02-06 2018-12-25 General Electric Company Coincidence-enabling photon-counting detector
WO2019019041A1 (en) * 2017-07-26 2019-01-31 Shenzhen Xpectvision Technology Co., Ltd. Methods of making and using an x-ray detector

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20030075685A1 (en) * 1999-03-10 2003-04-24 Tsutomu Yamakawa Nuclear medical diagnostic apparatus
US20060086913A1 (en) * 2004-10-07 2006-04-27 Martin Spahn Digital radiographic unit and a method for taking radiographs in a digital radiographic unit
JP2007155360A (en) * 2005-11-30 2007-06-21 Hitachi Ltd Nuclear medical diagnosis device, and radiation detection method in nuclear medical diagnosis device

Family Cites Families (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH06102065B2 (en) * 1985-11-26 1994-12-14 株式会社島津製作所 Radiography device
US4897788A (en) * 1988-04-18 1990-01-30 General Electric Company Image correction for computed tomography to remove crosstalk artifacts
JP3418800B2 (en) * 1994-02-03 2003-06-23 株式会社原子力エンジニアリング How to reduce annihilation gamma rays in radiation measurement
EP1257847A1 (en) * 1999-10-08 2002-11-20 Mamea Imaging AB Method and arrangement relating to x-ray imaging
IL137580A (en) * 2000-07-30 2005-11-20 Integrated Detector & Electron Readout system for solid state detector arrays
FI119204B (en) * 2001-12-18 2008-08-29 Oxford Instr Analytical Oy Radiation detector, arrangement and method for measuring radioactive radiation, where continuous low-energy background noise has been reduced
EP1347309A3 (en) * 2002-03-20 2012-04-18 Hitachi, Ltd. Radiological imaging apparatus and method
US6994299B2 (en) * 2002-12-13 2006-02-07 Cmi-Promex, Inc. Railroad crossing apparatus having improved rail connection and improved flangeway floor geometry and method incorporating the same
US6950493B2 (en) * 2003-06-25 2005-09-27 Besson Guy M Dynamic multi-spectral CT imaging
JP4041040B2 (en) 2003-09-08 2008-01-30 ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー Radiation tomography equipment
US7233640B2 (en) * 2003-11-26 2007-06-19 General Electric Company CT detector having an optical mask layer
FR2864731B1 (en) * 2003-12-30 2006-02-03 Commissariat Energie Atomique RADIATION DETECTION SYSTEM FOR BETTER EVENT COUNTING
JP3978193B2 (en) * 2004-03-15 2007-09-19 ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー Crosstalk correction method and X-ray CT apparatus

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20030075685A1 (en) * 1999-03-10 2003-04-24 Tsutomu Yamakawa Nuclear medical diagnostic apparatus
US20060086913A1 (en) * 2004-10-07 2006-04-27 Martin Spahn Digital radiographic unit and a method for taking radiographs in a digital radiographic unit
JP2007155360A (en) * 2005-11-30 2007-06-21 Hitachi Ltd Nuclear medical diagnosis device, and radiation detection method in nuclear medical diagnosis device

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20130294573A1 (en) * 2008-11-26 2013-11-07 Analogic Corporation Method of and apparatus for continuous wave tomosynthesis using photon counting
US8824628B2 (en) * 2008-11-26 2014-09-02 Analogic Corporation Method of and apparatus for continuous wave tomosynthesis using photon counting
EP2730948A4 (en) * 2011-07-07 2015-04-08 Toshiba Kk Photon counting image detector, x-ray diagnosis apparatus, and x-ray computerized tomography apparatus
US9213108B2 (en) 2011-07-07 2015-12-15 Kabushiki Kaisha Toshiba Photon counting type image detector, X-ray diagnosis apparatus and X-ray computed tomography apparatus
WO2018133087A1 (en) * 2017-01-23 2018-07-26 Shenzhen Xpectvision Technology Co., Ltd. X-ray detectors capable of identifying and managing charge sharing
US10948613B2 (en) 2017-01-23 2021-03-16 Shenzhen Xpectvision Technology Co., Ltd. X-ray detectors capable of identifying and managing charge sharing

Also Published As

Publication number Publication date
US20100025593A1 (en) 2010-02-04
CN101600974B (en) 2013-03-13
CN101600974A (en) 2009-12-09
WO2008093275A3 (en) 2008-11-06
US8050385B2 (en) 2011-11-01

Similar Documents

Publication Publication Date Title
US8050385B2 (en) Event sharing restoration for photon counting detectors
US9532759B2 (en) X-ray CT apparatus, image processing apparatus, and image processing method
EP2041606B1 (en) Energy spectrum reconstruction
EP1926431B1 (en) Direct measuring and correction of scatter for ct
JP5920908B2 (en) Computerized tomography system that generates projection data with reduced low signal effects
US8055039B2 (en) System and method to obtain noise mitigated monochromatic representation for varying energy level
JP2011224341A (en) System and method of acquiring multi-energy ct imaging data
EP2002287A2 (en) Dynamic optimization of the signal-to-noise ratio of dual-energy attenuation data for reconstructing images
US9943279B2 (en) Methods and systems for task-based data generation and weighting for CT spectral imaging
WO2010061307A2 (en) Spectral imaging
JP7348376B2 (en) Medical processing equipment, X-ray CT system and processing program
EP1933708B1 (en) Efficient iterative four-dimensional cardiac cone-beam ct reconstruction
JP2008536138A (en) Energy distribution reconstruction in CT
JP2021010727A (en) X-ray ct system and medical processing device
EP1904835A1 (en) Multiple scatter correction
US20080253509A1 (en) Acquisition Parameter Optimization For Csct
JP7353882B2 (en) X-ray CT system and medical processing equipment
EP3773214B1 (en) Cross directional bilateral filter for ct radiation dose reduction
US20200205751A1 (en) Medical processing apparatus, x-ray diagnosis system, and medical processing method
US20240193829A1 (en) Processing apparatus and processing method
US20240180503A1 (en) Photon counting computed tomography apparatus and photon-counting ct-scanning condition setting method
US20240074715A1 (en) X-ray ct apparatus, data processing method, and storage medium
JP2023012246A (en) Medical image processing apparatus, x-ray ct apparatus, medical image processing method and program
JP2019075123A (en) Image processing apparatus and medical image taking apparatus

Legal Events

Date Code Title Description
WWE Wipo information: entry into national phase

Ref document number: 200880003815.8

Country of ref document: CN

WWE Wipo information: entry into national phase

Ref document number: 12523998

Country of ref document: US

NENP Non-entry into the national phase

Ref country code: DE