EP2979293A1 - Source de rayons x et système d'imagerie - Google Patents

Source de rayons x et système d'imagerie

Info

Publication number
EP2979293A1
EP2979293A1 EP14711938.2A EP14711938A EP2979293A1 EP 2979293 A1 EP2979293 A1 EP 2979293A1 EP 14711938 A EP14711938 A EP 14711938A EP 2979293 A1 EP2979293 A1 EP 2979293A1
Authority
EP
European Patent Office
Prior art keywords
anode
ray source
electrons
ray
collector
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.)
Withdrawn
Application number
EP14711938.2A
Other languages
German (de)
English (en)
Inventor
Svetlana GOSSMANN
Oliver Heid
Timothy Hughes
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.)
Siemens AG
Original Assignee
Siemens AG
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 Siemens AG filed Critical Siemens AG
Publication of EP2979293A1 publication Critical patent/EP2979293A1/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00—X-ray tubes
    • H01J35/02—Details
    • H01J35/16—Vessels; Containers; Shields associated therewith
    • H01J35/18—Windows
    • 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
    • A61B6/40—Arrangements for generating radiation specially adapted for radiation diagnosis
    • A61B6/4035—Arrangements for generating radiation specially adapted for radiation diagnosis the source being combined with a filter or grating
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00—X-ray tubes
    • H01J35/02—Details
    • H01J35/16—Vessels; Containers; Shields associated therewith
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J2235/00—X-ray tubes
    • H01J2235/06—Cathode assembly
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J2235/00—X-ray tubes
    • H01J2235/08—Targets (anodes) and X-ray converters
    • H01J2235/086—Target geometry
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J2235/00—X-ray tubes
    • H01J2235/12—Cooling
    • H01J2235/1225—Cooling characterised by method
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J2235/00—X-ray tubes
    • H01J2235/16—Vessels
    • H01J2235/165—Shielding arrangements
    • H01J2235/168—Shielding arrangements against charged particles

Definitions

  • the present invention relates to an X-ray source with an evacuable outer housing with a beam exit ⁇ window, an electron source for the emission of electrons and an anode for generating X-radiation. Furthermore, the invention relates to an imaging system with such an X-ray source.
  • X-ray sources are within an evacuated outer casing, a so-called X-ray tube, electric ⁇ NEN accelerated to an anode whose material is suitable for converting energy of the accelerated electrons into x-rays.
  • ⁇ X-ray radiation is coupled out of the X-ray source from ⁇ .
  • the radiation is then typically directed to an object to be examined and then measured with an X-ray imaging detector.
  • the use of such systems is widespread. For the diagnostic examination of human body parts, it is generally desirable to achieve the highest possible image quality with the lowest possible X-ray dose.
  • the most monochromatic possible X-ray radiation is advantageous in which the radiation consists essentially of characteristic X-radiation and only to the smallest possible extent from the Bremsstrahlung distributed over a wide energy range.
  • 7,436,931 B2 is given by the high-energy electrons penetrating the thin anode. These electrons are trapped in the anode support and the energy is dissipated by a coolant flowing through the support.
  • a disadvantage here is the high heat development within the anode support and the possible ⁇ speed of the formation of Bremsstrahlung in the anode support. The Bremsstrahlung generates a continuous background in the resulting X-ray spectrum, which extends to a limit energy that corresponds to the kinetic energy of the accelerated electrons. The proportion of monochro matic ⁇ , characteristic X-rays in the overall spectrum and the radiation dose is reduced by this effect. Due to the high heat development and the necessity ⁇ speed of a coolant flow, this solution is also inefficient heat technically inefficient and mechanically expensive.
  • the object of the invention is to provide an X-ray source for the generation ⁇ supply of monochromatic X-rays as possible, which avoids the disadvantages mentioned.
  • Another object of the invention is to provide an imaging system with a sol ⁇ Chen X-ray source.
  • the X-ray source comprises an evacuable outer housing with at least one X-ray-permeable beam exit window. It further comprises an electron source for emitting electrons along an electron beam direction, an anode for generating X-radiation, and a collector for capturing electrons passing through the anode.
  • the collector is part of an electrical see circuit for applying a negative potential at the collector in relation to a potential at the anode.
  • the beam exit window is arranged so that X-ray radiation can be coupled out through the beam exit window, which emerges from the anode at least in a partial region of an angular range of 130 degrees to 230 degrees to the electron beam direction.
  • the X-ray source according to the invention makes it possible to produce a substantially monochromatic X-ray radiation, since in the anode mainly characteristic X-radiation is generated in a narrow energy range.
  • the electrons penetrating the anode also contribute little to the formation of unwanted bremsstrahlung, since these electrons are first efficiently decelerated by the inventively designed collector and then collected.
  • the capture of the accelerated electrons by the collector is electrically efficient, and it is in the holder of the anode no additional coolant ⁇ channel to transport the kinetic energy of this anode film penetrating electrons needed.
  • the electrons Due to the negative in the operation in comparison to the anode electric potential of the collector, the electrons lose part of their kinetic energy before they impinge on the Mate ⁇ material of the collector. As a result, the bremsstrahlung formed in the material of the collector is minimized.
  • the collector prevents these electrons in Be ⁇ operating the X-ray source reach more components in which they can generate braking radiation, and it will prevent them from leaving the X-ray source. In particular, these electrons do not interact with the outer casing of the X-ray source due to their efficient trapping.
  • the beam exit window is arranged such that X-ray radiation can be extracted through this window, which emerges from the anode at least in a partial region of the angular range of 130 degrees to 230 degrees to the electron beam direction.
  • the decoupling takes place according to the invention on the side of the anode, which corresponds to the facing the electron beam, wherein the decoupled X-ray radiation through the window may include an angular range of up to +/- 50 degrees with the backward direction of the electron beam.
  • the imaging system includes a dung OF INVENTION ⁇ contemporary X-ray source, an arrangement for receiving an object to be examined and an X-ray detector.
  • the advantages of the imaging system are analogous to the advantages indicated for the X-ray source.
  • the object to be examined may be a human body, an animal body or a part of such a body.
  • the arrangement for receiving the object to be examined is then, for example, a patient's couch or an arrangement for receiving a body part.
  • the imaging system can also be designed for the measurement of components.
  • the arrangement for receiving an object to be examined may be a holder for a component.
  • the advantages of the imaging system of the invention are particularly evident in medical imaging, for in the diagnostic examination of human body parts, it is particularly important to achieve with the lowest possible Strahlenbe ⁇ utilization highest possible image quality and thus A possible ⁇ as precisely as medical diagnosis.
  • monochromatic X-ray sources as possible, a particularly good image quality can be achieved.
  • the advantage of monochromatic X-ray sources is particularly great in the field of mammography and angiography, since these methods are used to examine body parts in which differences in the attenuation of the X-ray radiation must be mapped.
  • the patient's radiation exposure may either be reduced or it can be dispensed with the otherwise necessary use healthy ⁇ ness harmful X-ray contrast agent.
  • the X-ray source may additionally have the following features:
  • the collector can be made thicker along the electron beam direction than the average penetration depth of the electrons at a kinetic energy of the electrons of 150 keV.
  • the maximum kinetic energy to which electrons are accelerated in x-ray sources is up to 150 keV in many x-ray sources. If the collector is designed to be thicker than the mean penetration depth of the electrons in the region of this electron energy then, during operation of the X-ray source, a substantial portion of the electrons will be trapped by this maximum energy from the collector.
  • the collector is brought to a negative potential during operation as envisaged, the electrons are decelerated prior to entry into the material of the collector, and accordingly an even greater proportion of the electrons are collected by the collector.
  • the proportion of the electrons collected by the collector in this embodiment is at least 1-1 / e and thus over 63%.
  • the material of the described collector may comprise an electrically conductive material, for example stainless steel
  • the collector may have a thickness of at least 1 mm along the electron beam direction. Preferably, the thickness is chosen so that the collector He ⁇ reaching electrons with their remaining kinetic Energy can not substantially effetdrin ⁇ the thickness of the collector ⁇ gen.
  • the collector can have a depression in the electron beam direction. Such a depression is advantageous for reliably collecting the accelerated electrons in the collector and for laterally escaping the electrons
  • the formation of a depression of the collector is expedient, since a certain proportion of the electrons are scattered at the anode and thus changed in their direction of flight.
  • a collector with a depression is particularly suitable for collecting as many scattered electrons as possible.
  • the recess described may be designed trapezoidal. Alternatively, the recess may also be configured rectangular, U-shaped or semicircular. It may have a depth of at least 3 cm, more preferably the depth may be between 5 cm and 15 cm.
  • the beam exit window can be arranged so that X-ray radiation can be coupled out through the beam exit window, which emerges from the anode at least in a partial region of an angular range of 170 degrees to 190 degrees to the electron beam direction. In this embodiment, therefore, only X-ray radiation is released, which leaves the anode at an angle of +/- 10 degrees with the backward direction of the electron beam. Through this narrow win ⁇ angle range an even better ratio of charac- genetic X-ray is reached on the disturbing continuous braking radiation.
  • the electron source can have a hole for the passage of X-ray radiation to be coupled out in a central region.
  • the electron source can be formed as an annular source ⁇ .
  • the X-ray radiation to be coupled out at the back can penetrate the electron source. penetrate and pass through this area from the anode to the beam extraction window.
  • the beam exit window can then be arranged such that only X-ray radiation can be extracted by the beam exit window, which exits the anode at an angle of 175 degrees to 185 degrees to the electron beam direction.
  • the x-ray source may comprise at least one control electrode for accelerating and / or focusing the electrons on the anode.
  • the X-ray source can also be several such
  • Control electrodes include.
  • the at least one control electric ⁇ de may be an electrode having a circular cross-section, for example it may take the form of one or several ⁇ ren segments of a spherical surface.
  • the voltage of the control electrode is preferably higher than the voltage of the
  • the anode can have a metallic layer comprising a material having an atomic number of at least 40 and its layer thickness is lower than the average penetration depth of the electrons in ⁇ A material of the metallic
  • the advantage of this embodiment is that a particularly high proportion of characteristic X-radiation is formed in a material with a relatively high atomic number.
  • Particularly suitable materials are molybdenum with an atomic number of 42 and tungsten with an atomic number of 74.
  • the advantage of the low layer thickness is that only a minimum of Bremsstrahlung is generated in the metallic film of the anode. The choice of
  • Layer thickness is dependent on the anode material, because the penetration depth is dependent on the anode material properties.
  • Advantageous layer thicknesses are, for example, in the range of up to 10 ⁇ m, particularly advantageously in the range of up to 5 ⁇ m.
  • a higher layer thickness is not needed because the deceleration and trapping of the anode penetrating electrons through the collector.
  • the anode may have an anode support which comprises a material having an atomic number of at most 15 and whose layer thickness is lower than the mean penetration depth of the electrons in the material of the anode support at a kineti ⁇ cal energy of the electrons of 150 keV.
  • the choice of a lightweight material for the anode support is advantageous because as well as in the anode support little Bremsstrahlung is generated because materials with low atomic numbers only have a low interaction with the electrons.
  • the anode support itself serves to hold the metallic layer of the anode and to ensure mechanical stability. Even with the support body contributes to the smallest possible thickness to avoid unwanted Bremsstrahlung.
  • the thickness of the holder can be chosen to be higher than the thickness of the metallic layer, since in a material of lower atomic number, the interaction of electrons is lower and thus the average penetration depth at a certain kinetic energy is higher than in the metallic
  • the electrical circuit may be configured so that the collector can be brought to an electrical potential during operation of the X-ray source, which by we ⁇ iquess half is lower than an electric poten ⁇ tial of the anode, the potentials of the collector and the anode in relation to the potential of the electron source are de ⁇ finiert and in relation to this reference potential are both positive. This potential difference ensures that the electrons which penetrate the anode lose a considerable part of the energy in the field between anode and collector on their way from the anode to the collector.
  • the electron source may be a field emission cathode or a hot cathode.
  • a field emission cathode is a so-called cold cathode ⁇ are emitted gene source typically by a very high local field in the evacuated space of the X-ray in the electron.
  • the electrons are emitted from the cathode material into the evacuated space under the influence of high temperature.
  • the anode can be used as a fixed anode, as a rotary anode and / or as
  • a rotary anode comprises a rotatably mounted, usually disk-shaped plate, which is rotated within the plate plane, that the electron beam nachei ⁇ nander different locations in the edge region of the plate meets, whereby a better cooling and a longer Le ⁇ life of the metallic anode layer is achieved.
  • an electrically conductive liquid is used as the anode layer ness, for example, contain low ⁇ refractory metals and alloys of gallium, indium and / or tin.
  • the anode may also comprise a plurality of metallic layers, which may for example contain different materials.
  • the metallic layers can be arranged side by side on a common support body.
  • An X-ray source with a plurality of anode materials can be designed such that, depending on the application, monochromatic X-ray radiation with different energy can be made available, depending on which of the anode materials is brought into the region of the electron beam.
  • the imaging system may additionally comprise a beam filter disposed between the beam exit window and the arrangement for receiving the object to be examined.
  • a beam filter can be a metallic layer, for example made of aluminum, rhodium, mono- lybdän, copper and / or tin, which serves to absorb the low-energy part of the continuous Bremsstrahlung.
  • FIG. 1 shows a schematic cross-section of an X-ray source according to the preferred embodiment
  • FIG. 2 shows the simulated angle dependence of the X-ray flux density of this X-ray source
  • FIG. 1 shows a schematic cross-section of an X-ray source according to the preferred embodiment
  • FIG. 2 shows the simulated angle dependence of the X-ray flux density of this X-ray source
  • FIG. 1 shows a schematic cross-section of an X-ray source according to the preferred embodiment
  • Fig. 3 is an imaging system with this X-ray source
  • An X-ray source 1 according to a preferred prevailsbei ⁇ play of the invention is shown as a schematic cross-section in Fig. 1.
  • This view shows a part of the outer housing 3, which can be sealed gas-tight, so that the interior of the X-ray source can be evacuated.
  • the formation of a Va ⁇ kuums is a prerequisite for the emission of electrons in this space and their acceleration in the direction of a predetermined location.
  • the outer housing 3 is provided with a Strahlaus ⁇ exit window 5, which serves the X-ray generated from the X-radiation decouple 9 source. 1
  • the jet exit window 5 is also sealed in a vacuum-tight manner against the outer housing 3.
  • a suitable material for the beam exit window 5 is, for example, beryllium.
  • an electron source 7, an anode 13 and a collector 19 and in this example two control electrodes 23, 24 are arranged.
  • the electron source is here a cold field emission cathode. It is ring-shaped and arranged so that X-ray radiation 9 formed at the anode can reach the beam exit window 5 through the interior of this ring.
  • the electron source 7, the anode 13, the collector 19 and the control electrodes 23, 24 are part of a non ge here ⁇ showed electrical circuit.
  • the electrons emitted from the electron source 7 into the vacuum electrons are accelerated by a 7 between the electron source and the anode 13 is deposited ⁇ electric potential difference in the direction of the anode 13 accelerates.
  • the Elektronenquel ⁇ le 7 is connected to ground, and is in operation, a voltage of 150 kV at the anode.
  • the two control electrodes 23, 24 are formed as parts of spherical surfaces and serve to accelerate the electron beam emitted from the electron source 7 in the direction of the anode 13 and to focus.
  • the first control electrode 23 is at a potential of 10 kV and the second Steuerelekt ⁇ rode 24 at a potential of 150 kV. The emitted
  • Electrons are thereby focused onto a focal spot 14 on the surface of the anode 13 and meet in this case ⁇ play along the electron beam direction 11 perpendicular to the surface of the anode 13.
  • the anode 13 is in the illustrated embodiment, a failed ⁇ benförmige anode 13 which has on the electron source supplied ⁇ side adjacent a metallic layer 15 for 2 ym thick Mo ⁇ lybdenum, which is applied to an anode support 17th
  • the anode support 17 here consists of a 15 ym thick diamond wheel. In the thin molybdenum layer, part of the energy of the accelerated electrons is converted into characteristic X-rays of molybdenum.
  • the exterior ⁇ tion of the characteristic X-ray radiation from the focal spot 14 of the electrons is initially isotropic in all directions Kunststoffrich ⁇ lines.
  • the energy of the characteristic X-radiation is at the energy of the K a transitions of molybdenum at 17.4 keV and the K ⁇ transitions at 19.6 keV. Due to the emission of characteristic X-radiation, a quasi-monochromatic radiation is thus provided in this energy range.
  • Another suitable anode material is, for example, tungsten, which is suitable for producing quasi-monochromatic X-radiation in the range from 59 keV to 67 keV.
  • the small layer thickness of the metallic layer 15 is chosen so that it is lower than the mean Eindringtie ⁇ fe of accelerated to an energy of 150 keV electrons in this material.
  • a minimum layer thickness of several ym is necessary so that a sufficient proportion of electrons for generating characteristic X-radiation can interact with the molybdenum.
  • the anode support 17 in this example consists of a diamond disk, so that only a small interaction with the accelerated electrons takes place due to the low atomic number of the support material.
  • the thickness of the anode support 17 is designed so small that a large An ⁇ part of the accelerated electrons penetrates the anode support 17. This remaining portion continues to move toward the collector 19 along the electron beam direction 11. The function of the collector 19 is to brake the remaining electric ⁇ nen and catch.
  • the collector 19 is at operation of the X-ray source 1 at an electrical potential which is negative in the Ver ⁇ relation to the potential of the anode 13.
  • the collector 19 is at a Potenti ⁇ al of 30 kV, so that the electrons in the distance between the anode 13 and the collector 19 are braked to a small proportion of their original kinetic energy.
  • the material of the collector 19 is designed so that a majority of the electrons in the collector 19 is collected.
  • the collector 19 is made of stainless steel ⁇ .
  • the thickness of the collector 19 in the electron beam direction 11 is also designed so that the highest possible absorption of the electrons takes place, in this example the wall thickness is 4 mm.
  • the geometric arrangement of the anode 13, the electron source 7 and the beam exit window 5 is configured in this example, that at the anode 13 resulting Röntgenstrah ⁇ ment in an advantageous angular range ⁇ , ⁇ with the electron beam direction 11 between 170 degrees and 190 degrees the beam exit window 5 can be coupled out.
  • this angular range ⁇ , ⁇ the X-ray radiation can pass through the opening of the electron source 7.
  • the geometry of the X-ray source 1 can also be designed so that
  • Radiation in a larger angle range ⁇ between 130 degrees and 230 degrees is coupled out through the beam exit window 5.
  • the electrons can be also conducted by a laterally arranged of the beam path electron source with- means of control electrodes in the direction of the anode such that the electron source is not in the field of personallykop ⁇ pelnden radiation.
  • the opening in the middle region of the electron source 7 may be chosen to be so large, or the electron source 7 may be arranged so close to the anode 13, that radiation in the angular range ⁇ between 130
  • the specified geometry of the decoupling and the selected angle range ⁇ , ⁇ of the decoupled X-ray radiation with the electron beam direction 11 ensures that the radiation emerging from the X-ray source 1 has the highest possible proportion of characteristic X-radiation 25 and has the smallest possible amount of Bremsstrahlung 27, so that the X-radiation is substantially quasi-monochromatic.
  • the influence of the extraction geometry on Caribbeanset ⁇ Zung of X-rays is illustrated in FIG. 2.
  • FIG. 2 comparatively shows the simulated X-ray flux density for the characteristic X-ray radiation 25 and for the Bremsstrahlung as a function of the angle with the electron beam direction 11 for the above-mentioned materials and
  • the flux density of the characteristic X-ray radiation 25 predominates over the Bremsstrahlung 27.
  • the flux density of the characteristic X-radiation 25 is significantly higher, so that the continuous Bremsstrahlung 27 only a weak background forms under the characteristic emission bands.
  • Particularly advantageous for the generation of a quasi-monochromatic radiation is the angular range ⁇ , ⁇ between 170 degrees and 190 degrees.
  • Fig. 3 shows a schematic cross section of an imaging system 30 having an X-ray source 1 after the advance be registered ⁇ preferred embodiment of the invention.
  • the imaging system 30 is here a mammography device used for radiological examination of the female breast.
  • the imaging system 30 includes the x-ray source 1, shown in greater detail in FIG. 1, which is suspended from a support post 31 via a support arm 33.
  • a height-adjustable support 38 is mounted and a likewise height-adjustable compression plate 37, which together form a An ⁇ order 39 for receiving an object to be examined 40, here the female breast.
  • the quasi-monochromatic X-ray radiation 9 generated by the X-ray source 1 is coupled out through the beam exit window 5 and passes through an X-ray source 1 arranged below
  • the beam filter 35 consists of a 30 ym thick molybdenum layer, which serves to a
  • the X-ray ⁇ radiation 9 passes through the compression plate 37 on the compressed breast 40.
  • the passing through the chest 40 ⁇ de proportion of the X-ray radiation 9 is measured by an here within the carrier 38 arranged X-ray detector 41 and a downstream Auslese not shown here - electronics into a diagnostically usable X-ray image.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Medical Informatics (AREA)
  • Engineering & Computer Science (AREA)
  • Radiology & Medical Imaging (AREA)
  • Molecular Biology (AREA)
  • Biophysics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Optics & Photonics (AREA)
  • Pathology (AREA)
  • Physics & Mathematics (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • X-Ray Techniques (AREA)
  • Apparatus For Radiation Diagnosis (AREA)

Abstract

L'invention concerne une source de rayons X (1) comprenant un boîtier extérieur (3) dans lequel le vide peut être fait et comportant au moins une fenêtre de sortie de rayonnement (5) perméable aux rayons X, une source d'électrons (7), une anode (13) et un collecteur (19) destiné à recueillir les électrons qui traversent l'anode. Le collecteur fait partie d'un circuit électrique destiné à appliquer un potentiel négatif à l'anode, et la fenêtre de rayonnement est disposée de sorte que les rayons X (9) peuvent sortir à travers la fenêtre de rayonnement, la sortie de l'anode s'effectuant en formant une angle (a) de 130 à 230 degrés par rapport à la direction du faisceau d'électrons. L'invention concerne aussi un système d'imagerie comprenant une source de rayons X selon l'invention, un dispositif pour effectuer une prise de vue d'un objet à analyser et un détecteur de rayons X.
EP14711938.2A 2013-05-03 2014-03-07 Source de rayons x et système d'imagerie Withdrawn EP2979293A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102013208103.0A DE102013208103A1 (de) 2013-05-03 2013-05-03 Röntgenquelle und bildgebendes System
PCT/EP2014/054407 WO2014177308A1 (fr) 2013-05-03 2014-03-07 Source de rayons x et système d'imagerie

Publications (1)

Publication Number Publication Date
EP2979293A1 true EP2979293A1 (fr) 2016-02-03

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Family Applications (1)

Application Number Title Priority Date Filing Date
EP14711938.2A Withdrawn EP2979293A1 (fr) 2013-05-03 2014-03-07 Source de rayons x et système d'imagerie

Country Status (7)

Country Link
US (1) US20160064177A1 (fr)
EP (1) EP2979293A1 (fr)
JP (1) JP2016518689A (fr)
KR (1) KR20160004383A (fr)
CN (1) CN105164784A (fr)
DE (1) DE102013208103A1 (fr)
WO (1) WO2014177308A1 (fr)

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EP3751594B1 (fr) * 2019-06-11 2024-08-28 Siemens Healthineers AG Tube a rayons x
WO2023137334A1 (fr) * 2022-01-13 2023-07-20 Sigray, Inc. Source de rayons x à microfocalisation pour générer des rayons x à faible énergie et flux élevé

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CN105164784A (zh) 2015-12-16
JP2016518689A (ja) 2016-06-23
KR20160004383A (ko) 2016-01-12
US20160064177A1 (en) 2016-03-03
DE102013208103A1 (de) 2014-11-06
WO2014177308A1 (fr) 2014-11-06

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