WO2008044194A2 - Electron optical apparatus, x-ray emitting device and method of producing an electron beam - Google Patents

Electron optical apparatus, x-ray emitting device and method of producing an electron beam Download PDF

Info

Publication number
WO2008044194A2
WO2008044194A2 PCT/IB2007/054087 IB2007054087W WO2008044194A2 WO 2008044194 A2 WO2008044194 A2 WO 2008044194A2 IB 2007054087 W IB2007054087 W IB 2007054087W WO 2008044194 A2 WO2008044194 A2 WO 2008044194A2
Authority
WO
WIPO (PCT)
Prior art keywords
electron
electrons
anode
emitter
magnetic
Prior art date
Application number
PCT/IB2007/054087
Other languages
French (fr)
Other versions
WO2008044194A3 (en
Inventor
Stefan Hauttmann
Wolfram Maring
Steffen Holzapfel
Original Assignee
Philips Intellectual Property & Standards Gmbh
Koninklijke Philips Electronics N.V.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Philips Intellectual Property & Standards Gmbh, Koninklijke Philips Electronics N.V. filed Critical Philips Intellectual Property & Standards Gmbh
Priority to AT07826677T priority Critical patent/ATE496389T1/en
Priority to DE602007012126T priority patent/DE602007012126D1/en
Priority to EP07826677A priority patent/EP2074642B1/en
Priority to US12/444,745 priority patent/US7839979B2/en
Publication of WO2008044194A2 publication Critical patent/WO2008044194A2/en
Publication of WO2008044194A3 publication Critical patent/WO2008044194A3/en

Links

Classifications

    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00—X-ray tubes
    • H01J35/24—Tubes wherein the point of impact of the cathode ray on the anode or anticathode is movable relative to the surface thereof
    • H01J35/30—Tubes wherein the point of impact of the cathode ray on the anode or anticathode is movable relative to the surface thereof by deflection of the cathode ray
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00—X-ray tubes
    • H01J35/02—Details
    • H01J35/14—Arrangements for concentrating, focusing, or directing the cathode ray
    • H01J35/153—Spot position control
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00—X-ray tubes
    • H01J35/02—Details
    • H01J35/14—Arrangements for concentrating, focusing, or directing the cathode ray
    • H01J35/147—Spot size control

Definitions

  • the present invention relates to an electron optical apparatus for producing an electron beam, to an X-ray emitting device and to a method of producing an electron beam.
  • CT computer tomograph
  • CV cardiovascular
  • the thermal load of the target is in this case determined only by electrons contributing to the tube's X-ray output.
  • the backscattered electrons release their energy at the SEC which is integrated into the tube's cooling system.
  • this setup including a SEC enhances the distance between anode and cathode but leaves no space for focusing elements. Compared to prior X-ray tubes this causes a drastically enlarged electron beam path making the focusing of the electron beam more advanced.
  • Image quality issues in CT or CV imaging require the possibility of an active control of the focal spot size during image acquisition.
  • New imaging modalities in CT like dynamic focal spot (deflection in tangential and radial direction) which help to increase spatial resolution or to reduce artifacts need in addition the ability of active focal spot position control.
  • an electron optical apparatus comprising the following components along an optical axis, preferably in the indicated order: a cathode including an emitter having a planar surface for emitting electrons; an anode for accelerating the emitted electrons in a direction essentially along the optical axis; a first magnetic quadrupole lens for deflecting the accelerated electrons and having a first yoke; a second magnetic quadrupole lens for further deflecting the accelerated electrons and having a second yoke; and a magnetic dipole lens for further deflecting the accelerated electrons.
  • This aspect of the invention is based on the idea to combine into an electron optical apparatus the advantages of a double quadrupole lens consisting of a first magnetic quadrupole lens and a second magnetic quadrupole lens and the advantages of a thin, flat and unstructured or only slightly structured emitter.
  • the double quadrupole provides excellent focusing properties.
  • the flat emitter having a planar surface for emitting electrons provides for a reduced lateral energy component of the emitted electrons thereby also contributing to excellent focusing properties of the electron optical apparatus.
  • a magnetic dipole lens is provided for deflecting the emitted electrons in transversal and radial directions.
  • an electron apparatus shall be defined as comprising both a cathode including an emitter as a source of free electrons, an anode for accelerating the provided free electrons thereby creating a beam of electrons, and an electron optics for deflecting the accelerated free electrons thereby focusing and/or deflecting the beam of electrons.
  • the main direction into which the free electrons are accelerated by the anode can be defined as an optical axis of the electron optical apparatus.
  • the emitter has a substantially planar surface for emitting electrons.
  • substantially planar means that the surface includes no significant curvatures, openings or protrusions and is substantially flat, smooth and substantially unstructured.
  • there may be fine structures within the planar surface such as grooves or recesses.
  • the depth of such structures may be significantly less than the dimensions of the surface.
  • the depth of the structures can be less than 10%, preferably less than 1%, of the length of the surface.
  • the emitter can be in the form of an flat foil.
  • the emitter can be prepared with a refractory and electrically conductive material such as for example tungsten or a tungsten alloy.
  • the emitter can be heated by applying a voltage and thereby inducing a heating current within the emitter. Preferable the current is induced such that the emitting surface of the emitter is heated homogeneously. From the heated surface of the cathode electrons can be emitted. As the emitting surface of the cathode is planar the electrons can be emitted homogeneously. The average direction of electrons exiting from the emitting surface can be the same all over the emitting surface. With conventional cathodes including e.g.
  • tungsten coils or flat tungsten emitters with slits the non-planar structure of the cathode heavily distorts the electric potential between the cathode and the anode thereby increasing the velocity component of electrons transverse to the optical axis and hence increasing the focal spot size of the electron optical apparatus.
  • an electric potential applied between the cathode and the anode can be homogeneous and is not distorted by structures on the cathode. Accordingly, electrons homogeneously emitted from the cathode surface can all be homogeneously accelerated along or parallel to the optical axis of the apparatus. This can contribute to a minimal focal spot of the electron optical apparatus.
  • the anode can be any conventional anode usable for generating an electric potential between the anode and the cathode.
  • the electrical anode can have an opening in a region around the optical axis such that electrons accelerated within the generated potential can fly through this opening in the anode.
  • the anode can have the form of a cup having an opening at the center.
  • the cup can disembogue in a bottle neck which extends around the opening in a direction away from the cathode.
  • the first and the second magnetic quadrupole lenses can be constituted by electromagnetic devices which are arranged in a way to produce a magnetic quadrupole field.
  • four magnetic poles can be arranged at the corners of a square such that two magnetic south poles are arranged on diagonally opposite corners of the square and two magnetic north poles are arranged on the other corners.
  • Electromagnetic coils for the first and second magnetic lens can be arranged on first and second yokes, respectively.
  • the yokes can be prepared with a ferromagnetic material for enhancing the created magnetic field.
  • the yokes can have a geometry adapted such as to hold the electromagnetic coils at positions so as to create a magnetic quadrupole field.
  • the yokes can have a rectangular, square or round geometry.
  • the yokes can have protrusions on which the electromagnetic coils are located.
  • the first and the second magnetic quadrupole lenses can have substantially the same geometry.
  • the two lenses are arranged in parallel with respect to each other.
  • each of the lenses can be arranged perpendicular to the optical axis.
  • the purpose of the first and the second magnetic quadrupole lenses is to deflect the accelerated electrons such that the electron beam can be finally focused onto a probe.
  • Each quadrupole lens creates a magnetic field having a gradient. I.e. the magnetic field intensity differs within the magnetic field. Equipotential surfaces of the quadrupole field can have a hyperbolic form.
  • the gradient of a magnetic quadrupole is such that the magnetic quadrupole field acts as focusing the electron beam in a first direction whereas it acts as defocusing in a second direction perpendicular to the first direction.
  • the two quadrupole lenses can be arranged such that their magnetic field gradients are rotated about 90° with respect to each other.
  • the magnetic fields of the first and the second magnetic quadrupole lenses might have a symmetry with respect to the optical axis or with respect to a plane through the optical axis.
  • the magnetic dipole lens can be provided by one or more magnetic dipole coils.
  • two magnetic coils can be provided. They can be arranged in a plane perpendicular to the optical axis of the electron optical apparatus and at opposite positions with respect to the optical axis.
  • the purpose of the dipole lens is to provide a substantially homogeneous magnetic field in order to deflect the accelerated electrons in a way so as to shift the focus of the electron beam on a probe.
  • the magnetic dipole lens comprises dipole coils which are arranged on the yoke of the second magnetic quadrupole lens.
  • the magnetic dipole field can be directly superimposed to the magnetic quadrupole field of the second quadrupole lens.
  • the second yoke can serve both as a yoke for the second quadrupole lens and as a yoke for the dipole lens.
  • the electron optical apparatus comprises a scattered electron collector (SEC).
  • the SEC is adapted to collect backscattered electrons created on the impact of accelerated electrons coming from the electron optical apparatus.
  • the accelerated electrons hit the surface of a probe such as an anode disc of an X-ray emitting device. Some of these electrons are reflected. Other electron free secondary electrons from the probe. All these backscattered electrons fly away from the probe and to the SEC where they are collected.
  • the SEC can be positioned downstream of the second quadrupole lens i.e. at an end of the electron optical apparatus opposite to the cathode.
  • the SEC can be prepared with an electrically conductive material. An electric voltage can be applied to the SEC such that the SEC and the anode are on the same electric potential.
  • the SEC can be electrically connected to the anode.
  • the SEC can have the form of an inverse cup having an opening in a center through which the electron beam can pass.
  • the SEC can be continuous to a bottle neck of the anode cup.
  • each of the components such as the cathode including the emitter, the anode, the first and the second magnetic quadrupole lenses and the magnetic dipole lens and optionally the scattered electron collector has a symmetry with respect to the optical axis.
  • the components can be arranged co-axially with respect to the optical axis. Using such symmetrical arrangement the design of the electron optical apparatus can be simplified. Furthermore, a defined and symmetric focal spot can be achieved.
  • the electron optical apparatus has a length along the optical axis of less than 90mm and preferably between 70mm and 90mm. Including the scattered electron collector the length of the electron optical apparatus can be adapted to be no longer than 150mm or preferably between 120mm and 150mm. This short length can be achieved by using flat space saving components such as the flat emitter and by advantageously arranging the components of the apparatus.
  • the magnetic dipole lens can be integrated into the second quadrupole lens thereby saving space in the direction of the optical axis. Having such short length the electron optical apparatus is particularly well suited for applications with space or weight restrictions such as CT or CV applications.
  • the planar surface of the emitter is non- structured.
  • the surface of the emitter from which the electrons can be emitted towards the anode is a homogeneous plane without any recesses or protrusions. Electrons can be emitted homogeneously from such non- structured surface.
  • such non-structured emitter surface does not disturb the electric field between the cathode including the emitter and the anode. Especially the electric field close to the surface of the emitter is not disturbed by any structures. Accordingly, electric field lines remain linear and electrons are accelerated parallely to the optical axis without any substantial transversal moving component. The electron beam is not widened. This can help in better focusing of the electron beam.
  • the planar surface of the emitter is finely structured.
  • fine structures such as e.g. grooves, slits or recesses are located within the planar surface of the emitter.
  • These fine structures can be used e.g. for confining an electrical current within the emitter which is used to electrically heat the emitter.
  • the size and/or arrangement of such fine structures can be chosen such that the emitted electrons are not excessively scattered and such that the electric field is not excessively distorted.
  • an X-ray emitting device comprising the following component along an optical axis: an electron optical apparatus as described above; and an anode disc arranged such that the accelerated electrons impact on a electron receiving surface of the anode disc.
  • the anode disc can have a slanted surface onto which the electron beam coming from the electron optical apparatus can be directed. Electrons impacting the surface of the anode disc and entering the anode material produce X-ray radiation.
  • the angle of the slanted surface of the anode disc can be selected such that the X-rays are emitted transversely, preferably perpendicularly, to the optical axis of the electron optical apparatus.
  • the anode disc can be prepared with a selected material in order to receive desired X-ray characteristics.
  • the anode disc can be rotated about an axis parallel to the optical axis of the electron optical apparatus.
  • the electrical anode and the anode disc are essentially on the same electric potential.
  • this SEC can be set on the electrical potential of the anode.
  • the region between the anode and the anode disc can be free of any electric field. By eliminating any electric field in the proximity of the surface of the anode disc it can be prevented that backscattered electrons coming from the surface of the anode disc are reattracted towards the anode disc. Otherwise, these reattracted backscattered electrons would unnecessarily widen the focal spot and would furthermore contribute to heating of the anode disc thereby increasing the cooling requirements for the anode disc.
  • the cathode including the emitter, the electrical anode, the first magnetic quadrupole lens, the second magnetic quadrupole lens, the optional scattered electron collector and the anode disc are all connected to a water cooling circuit.
  • a combined water cooling circuit can be used for cooling all component except the cathode including the emitter.
  • the water in the cooling circuit is electrically conductive but when the mentioned components are preferably all on ground potential no further measures for electrically insulating the cooling circuit and the components has to be provided.
  • a distance from the electron emitting surface of the emitter to a electron receiving surface of the anode disc is less than 150mm and preferably between 120mm and 150mm. As outlined above, this can be achieved by special selection of the constituent component and the arrangement of the components.
  • a medical X-ray device comprising an X-ray emitting device as outlined above.
  • the medical X-ray device can be for example a computer tomograph or a cardiovascular imaging device.
  • Such medical devices can have severe requirements in terms of focal spot size, control of the focal spot size, ratio and position, cooling down times and, concerning CTs, gantry rotation times. Using an X-ray emitting device as outlined above these requirements can be met.
  • a method of creating an electron beam comprising the steps of: emitting electrons from a planar surface of a emitter; accelerating the electrons in a direction essentially parallel to the optical axis using an anode; deflecting the accelerated electrons using a first magnetic quadrupole lens; further deflecting the accelerated electrons using a second magnetic quadrupole lens; further deflecting the accelerated electrons using a magnetic dipole lens.
  • Exemplary embodiments of the present invention are described with reference to an electron optical apparatus or an X-ray emitting device.
  • Fig. Ia shows a schematic setup of an X-ray emitting device according to the present invention in cross-section perpendicular to a width direction.
  • Fig. Ib shows the schematic setup of Fig Ia in cross-section perpendicular to a length direction.
  • Fig. 2 shows a magnetic quadrupole lens which can be used as first magnetic quadrupole lens in the setup of Fig. Ia.
  • Fig. 3 shows a magnetic quadrupole lens including a magnetic dipole lens which can be used as second magnetic quadrupole lens in the setup ofFig. Ia.
  • Fig. 4 shows a diagram indicating length and width of area-minimized focal spots for different tube currents achievable with an X-ray emitting device according to the invention.
  • Fig. 5 visualizes different focal spots for CT applications.
  • Fig. 6 visualizes different focal spot positions achieved by applying specific currents to the magnetic dipole lens of an X-ray emitting device according to the invention.
  • Fig. 7 schematically shows a computer tomography device according to the invention.
  • Fig. Ia and Ib show an embodiment of an X-ray emitting device 1 according to the invention.
  • the proposed X-ray emitting device to reach the above requirements comprises a cathode with a flat emitter 3 as an electron source and a lens system 5.
  • the objective of spot control is to create a line focus (an elongated spot) on the slanted part of an anode disc 7 in such a way that the effective X-ray source has an approximately equal size in width and length dimension when viewed from an X-ray exit window.
  • the spot length has to be enlarged by a factor (typically around 8) with respect to the width depending on the anode slant angle (typically around 8°).
  • the first essential step is to reduce the tangential energy components of the emitted electrons. This is reached by emitting the electrons from a flat, smooth and unstructured tungsten or tungsten alloy foil emitter within the cathode 3 which is directly heated by an applied electrical current.
  • the emitter 3 has a planar surface 9 directed towards an anode 11.
  • a first pre-focusing element in length and width direction is given by a cathode cup 13 with a ring on high potential.
  • the entrance into the electrical anode opening 15 acts as a second optical element having an isotropic defocusing effect.
  • the main optical component the double magnetic quadrupole lens including a first magnetic quadrupole lens 19 and a second magnetic quadrupole lens 21, is positioned approximately in the middle between the cathode 3 and the target anode disc 7 around the bottle-neck 17. It consists of a cathode side first quadrupole lens 19 and an anode side second quadrupole lens 21 with integrated dipole lens 23 enabling a shifting of the focal spot in x/z-direction, i.e. a plane perpendicular to an optical axis 25 of the X-ray device 1.
  • the first magnetic quadrupole lens 19 focuses in length and defocuses in width direction of the focal spot.
  • the electron beam is then focused in width direction and defocused in length direction by the following second quadrupole lens 21.
  • the two sequentially arranged magnetic quadrupole lenses guarantee a net focusing effect in both directions of the focal spot which is also demonstrated in Fig. 1.
  • This mode of operation of the double magnetic quadrupole lens leads to the required narrow line focus on the target anode disc 7 with typical length to width relations between 7 and 10.
  • Fig. Ib the region (a) indicates an emitting and acceleration length, the region (b) indicates a focusing and beam shaping length and the region (c) indicates a scattered electron collector and heat management length.
  • Fig. 2 shows a top view of the first magnetic quadrupole lens 19.
  • a square yoke 41 comprises protrusions 43 directed to the center of the square. On each of these four protrusions 43 a magnetic coil 45 is provided.
  • FIG. 3 shows a top view of the second magnetic quadrupole lens 21.
  • a square yoke 51 comprises protrusions 53 directed to the center of the square.
  • a magnetic coil 55 is provided on each of these four protrusions 53 .
  • 57 for forming a magnetic dipole lens 23 is arranged in the center of each of the longitudinal arms of the square yoke 51.
  • the disclosed setup requires a beam path length of approximately
  • Fig. 4 as a function of tube current. It is obvious that these foci are outstanding small with respect to the tube currents in comparison to every other X-ray tube used today for medical examinations. Enlarging these minimal focal spots by independently changing length and width at a given tube current can easily be done by only controlling the coil currents of the two magnetic quadrupole lenses 19, 21.
  • the focal spot width enlarges by 50% and the focal spot length by 100% for the smallest spot.
  • the stronger influence on the length is caused by electrons emitting from the inner slit walls which are orientated in width direction. For a commonly used coil emitter this effect even drastically increases:
  • Fig. 5a shows a IEC 03 focal spot for CV applications
  • Fig. 5b shows a 0.75x0.9mm 2 focal spot for CT applications
  • Fig. 5c shows a 1.30x1.45mm 2 focal spot for CT applications.
  • Fig. 7 shows a computer tomography apparatus 100, which is also called a CT scanner and in which the above X-ray emitting device can be used.
  • the CT scanner 100 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 105 designates a source of radiation such as an X-ray emitting device as described above, which emits polychromatic radiation 107.
  • the CT scanner 100 further comprises an aperture system 106, which forms the X-radiation being emitted from the X-ray source 105 into a radiation beam 107.
  • the spectral distribution of the radiation beam emitted from the radiation source 105 may further be changed by a filter element (not shown), which is arranged close to the aperture system 106.
  • the radiation beam 107 which may by a cone-shaped or a fan-shaped beam 107, is directed such that it penetrates a region of interest 110a such as a head 11 Oa of a patient 110.
  • the patient 110 is positioned on a table 112.
  • the patient's head 110a is arranged in a central region of the gantry 101, which central region represents the examination region of the CT scanner 100.
  • the radiation beam 107 After penetrating the region of interest 110a the radiation beam 107 impinges onto a radiation detector 115.
  • a not depicted anti scatter grid In order to be able to suppress X-radiation being scattered by the patient's head 110a and impinging onto the X-ray detector under an oblique angle there is provided a not depicted anti scatter grid.
  • the anti scatter grid is preferably positioned directly in front of the detector 115.
  • the X-ray detector 115 is arranged on the gantry 101 opposite to the X- ray tube 105.
  • the detector 115 comprises a plurality of detector elements 115a wherein each detector element 115a is capable of detecting X-ray photons, which have been passed through the head 110a of the patient 110.
  • the X-ray source 105, the aperture system 106 and the detector 115 are rotated together with the gantry 101 in a rotation direction indicated by an arrow 117.
  • the motor 103 is connected to a motor control unit 120, which itself is connected to a data processing device 125.
  • the data processing device 125 includes a reconstruction unit, which may be realized by means of hardware and/or by means of software.
  • the reconstruction unit is adapted to reconstruct a 3D image based on a plurality of 2D images obtained under various observation angles.
  • the data processing device 125 serves also as a control unit, which communicates with the motor control unit 120 in order to coordinate the movement of the gantry 101 with the movement of the table 112.
  • a linear displacement of the table 112 is carried out by a motor 113, which is also connected to the motor control unit 120.
  • the gantry 101 rotates and in the same time the table 112 is shifted linearly parallel to the rotational axis 102 such that a helical scan of the region of interest 110a is performed. It should be noted that 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. Thereby, slices of the head 110a may be measured with high accuracy. A larger three-dimensional representation of the patient's head may be obtained by sequentially moving the table 112 in discrete steps parallel to the rotational axis 102 after at least one half gantry rotation has been performed for each discrete table position.
  • the detector 115 is coupled to a pre-amplif ⁇ er 118, which itself is coupled to the data processing device 125.
  • the processing device 125 is capable, based on a plurality of different X-ray projection datasets, which have been acquired at different projection angles, to reconstruct a 3D representation of the patient's head 110a.
  • a display 126 is provided, which is coupled to the data processing device
  • arbitrary slices of a perspective view of the 3D representation may also be printed out by a printer 127, which is also coupled to the data processing device
  • the data processing device 125 may also be coupled to a picture archiving and communications system 128 (PACS).
  • PACS picture archiving and communications system
  • monitor 126 the printer 127 and/or other devices supplied within the CT scanner 100 might be arranged local to the computer tomography apparatus 100. Alternatively, these components may be remote from the
  • CT scanner 100 such as elsewhere within an institution or hospital, or in an entirely different location linked to the CT scanner 100 via one ore more configurable networks, such as the Internet, virtual private networks and so forth.
  • configurable networks such as the Internet, virtual private networks and so forth.
  • the electron optical concept comprising a flat unstructured or even fine-structured flat emitter and two magnetic quadrupole lenses, provides all features necessary for medical X-ray examinations without exceeding geometrical space and weight restrictions due to its small size.
  • the electron optical concept comprises a non-structured or fine structured thin flat emitter and a magnetic double quadrupole lens with dipole coils on the anode- side yoke within a length of 70-90mm and a total optical length from emitter to target between 120mm and 150mm.
  • the 50-60mm in length between the double quadrupole lens and the target are lens-free and could comprise a scattered-electron-collector (SEC).
  • This concept can provide e.g. focal spots variable in width between 0.2- 1.3mm with arbitrary values in focal spot length between 0.23- 1.45mm for tube currents of 100-160OmA and high voltages of 70-14OkV necessary for medical X-ray applications. Additionally it is possible to quickly shift these foci in radial and tangential direction which leads to higher spatial resolutions.
  • the invention would be applicable to any field in which electrons have to be focused with variable focal spot sizes, shapes and positions combined with high currents but only a limited space for optical elements is available.
  • This electron- optical concept provides the following advantages: 1) focusing high current electron beams into the required line shaped small focal spots with a typical ratio of 7-10 between length and width perpendicular to the optical axis, 2) retaining focusing properties over a large range of kV and mA, 3) independent control of focal spot width and length, and 4) active control of focal spot size and position.

Landscapes

  • X-Ray Techniques (AREA)
  • Particle Accelerators (AREA)
  • Gear Transmission (AREA)
  • Analysing Materials By The Use Of Radiation (AREA)
  • Electron Sources, Ion Sources (AREA)

Abstract

It is described an electron optical arrangement, a X-ray emitting device and a method of creating an electron beam. An electron optical apparatus (1) comprises the following components along an optical axis (25): a cathode with an emitter (3) having a substantially planar surface (9) for emitting electrons; an anode (11) for accelerating the emitted electrons in a direction essentially along the optical axis (25); a first magnetic quadrupole lens (19) for deflecting the accelerated electrons and having a first yoke(41); a second magnetic quadrupole lens (21) for further deflecting the accelerated electrons and having a second yoke(51); and a magnetic dipole lens (23) for further deflecting the accelerated electrons.

Description

ELECTRON OPTICAL APPARATUS, X-RAY EMITTING DEVICE AND METHOD OF PRODUCING AN ELECTRON BEAM
FIELD OF THE INVENTION
The present invention relates to an electron optical apparatus for producing an electron beam, to an X-ray emitting device and to a method of producing an electron beam.
TECHNICAL BACKGROUND
The future demands for high-end computer tomograph (CT) and cardiovascular (CV) imaging regarding the X-ray source are (1) higher power/tube current, (2) smaller focal spots combined with the ability of active control of the size, ratio and position of the focal spot, (3) shorter times for cooling down, and, concerning CT, (4) shorter gantry rotation times. In addition to this, the tube design is limited in length and weight to achieve an easy handling for CV applications and a realisable gantry setup for CT applications.
One key to reach higher power and faster cooling is given by using a sophisticated heat management concept inside the X-ray tube. In conventional bipolar X-ray tubes about 40% of the thermal load of the target is due to electrons backscattered from the target, which are reaccelerated towards the target and hitting it again outside the focal spot. Hence these electrons contribute to the temperature increase of the target and cause off- focal radiation. Therefore one key component of a currently developed new X-ray tube generation is a scattered electron collector (SEC) located in front of the target. Introducing this component in combination with a unipolar tube setup causes an electrical field- free region above the target if both elements - target and SEC - are on the same potential. The thermal load of the target is in this case determined only by electrons contributing to the tube's X-ray output. The backscattered electrons release their energy at the SEC which is integrated into the tube's cooling system. Conventionally, this setup including a SEC enhances the distance between anode and cathode but leaves no space for focusing elements. Compared to prior X-ray tubes this causes a drastically enlarged electron beam path making the focusing of the electron beam more advanced. One major goal of new high-end X-ray tubes for medical examinations is to provide variable and small focal spot sizes and positions within a high voltage range of U=60-150kV and tube currents up to I=2A. Additionally limitations in the tube size with an optical length of 1< 13 Omm have to be taken into account.
Image quality issues in CT or CV imaging require the possibility of an active control of the focal spot size during image acquisition. New imaging modalities in CT like dynamic focal spot (deflection in tangential and radial direction) which help to increase spatial resolution or to reduce artifacts need in addition the ability of active focal spot position control.
For satisfying the above and other requirements, there may be a need for an improved electron optical apparatus for producing an electron beam, an improved X- ray emitting device and an improved method for producing an electron beam. SUMMARY OF THE INVENTION
This need may be met by the subject matter according to the independent claims. Advantageous embodiments of the present invention are described by the dependent claims.
According to a first aspect of the invention there is provided an electron optical apparatus comprising the following components along an optical axis, preferably in the indicated order: a cathode including an emitter having a planar surface for emitting electrons; an anode for accelerating the emitted electrons in a direction essentially along the optical axis; a first magnetic quadrupole lens for deflecting the accelerated electrons and having a first yoke; a second magnetic quadrupole lens for further deflecting the accelerated electrons and having a second yoke; and a magnetic dipole lens for further deflecting the accelerated electrons.
This aspect of the invention is based on the idea to combine into an electron optical apparatus the advantages of a double quadrupole lens consisting of a first magnetic quadrupole lens and a second magnetic quadrupole lens and the advantages of a thin, flat and unstructured or only slightly structured emitter. The double quadrupole provides excellent focusing properties. The flat emitter having a planar surface for emitting electrons provides for a reduced lateral energy component of the emitted electrons thereby also contributing to excellent focusing properties of the electron optical apparatus. Furthermore, to fulfill the requested variable focus spot position, a magnetic dipole lens is provided for deflecting the emitted electrons in transversal and radial directions.
In the following, features and advantages of the electron optical apparatus according to the first aspect will be described in detail. Herein, an electron apparatus shall be defined as comprising both a cathode including an emitter as a source of free electrons, an anode for accelerating the provided free electrons thereby creating a beam of electrons, and an electron optics for deflecting the accelerated free electrons thereby focusing and/or deflecting the beam of electrons. The main direction into which the free electrons are accelerated by the anode can be defined as an optical axis of the electron optical apparatus.
The emitter has a substantially planar surface for emitting electrons. Herein, "substantially planar" means that the surface includes no significant curvatures, openings or protrusions and is substantially flat, smooth and substantially unstructured. However, there may be fine structures within the planar surface such as grooves or recesses. The depth of such structures may be significantly less than the dimensions of the surface. For example, the depth of the structures can be less than 10%, preferably less than 1%, of the length of the surface. The emitter can be in the form of an flat foil. The emitter can be prepared with a refractory and electrically conductive material such as for example tungsten or a tungsten alloy. The emitter can be heated by applying a voltage and thereby inducing a heating current within the emitter. Preferable the current is induced such that the emitting surface of the emitter is heated homogeneously. From the heated surface of the cathode electrons can be emitted. As the emitting surface of the cathode is planar the electrons can be emitted homogeneously. The average direction of electrons exiting from the emitting surface can be the same all over the emitting surface. With conventional cathodes including e.g. tungsten coils or flat tungsten emitters with slits the non-planar structure of the cathode heavily distorts the electric potential between the cathode and the anode thereby increasing the velocity component of electrons transverse to the optical axis and hence increasing the focal spot size of the electron optical apparatus.
In an electron apparatus according to the present invention, as the emitting surface of the cathode is essentially planar an electric potential applied between the cathode and the anode can be homogeneous and is not distorted by structures on the cathode. Accordingly, electrons homogeneously emitted from the cathode surface can all be homogeneously accelerated along or parallel to the optical axis of the apparatus. This can contribute to a minimal focal spot of the electron optical apparatus.
The anode can be any conventional anode usable for generating an electric potential between the anode and the cathode. The electrical anode can have an opening in a region around the optical axis such that electrons accelerated within the generated potential can fly through this opening in the anode. For example the anode can have the form of a cup having an opening at the center. The cup can disembogue in a bottle neck which extends around the opening in a direction away from the cathode. The first and the second magnetic quadrupole lenses can be constituted by electromagnetic devices which are arranged in a way to produce a magnetic quadrupole field. For example, four magnetic poles can be arranged at the corners of a square such that two magnetic south poles are arranged on diagonally opposite corners of the square and two magnetic north poles are arranged on the other corners.
Electromagnetic coils for the first and second magnetic lens can be arranged on first and second yokes, respectively. The yokes can be prepared with a ferromagnetic material for enhancing the created magnetic field. The yokes can have a geometry adapted such as to hold the electromagnetic coils at positions so as to create a magnetic quadrupole field. For example, the yokes can have a rectangular, square or round geometry. The yokes can have protrusions on which the electromagnetic coils are located. The first and the second magnetic quadrupole lenses can have substantially the same geometry. Preferably, the two lenses are arranged in parallel with respect to each other. Furthermore, each of the lenses can be arranged perpendicular to the optical axis.
The purpose of the first and the second magnetic quadrupole lenses is to deflect the accelerated electrons such that the electron beam can be finally focused onto a probe. Each quadrupole lens creates a magnetic field having a gradient. I.e. the magnetic field intensity differs within the magnetic field. Equipotential surfaces of the quadrupole field can have a hyperbolic form. The gradient of a magnetic quadrupole is such that the magnetic quadrupole field acts as focusing the electron beam in a first direction whereas it acts as defocusing in a second direction perpendicular to the first direction. The two quadrupole lenses can be arranged such that their magnetic field gradients are rotated about 90° with respect to each other. After traversing both magnetic quadrupole lenses a line focus can be achieved which means that the electron beam is focused to an elongated spot having a length to width ratio of e.g. more than 5. For this purpose, the magnetic fields of the first and the second magnetic quadrupole lenses might have a symmetry with respect to the optical axis or with respect to a plane through the optical axis.
The magnetic dipole lens can be provided by one or more magnetic dipole coils. In order to obtain a homogeneous magnetic dipole field, two magnetic coils can be provided. They can be arranged in a plane perpendicular to the optical axis of the electron optical apparatus and at opposite positions with respect to the optical axis.
The purpose of the dipole lens is to provide a substantially homogeneous magnetic field in order to deflect the accelerated electrons in a way so as to shift the focus of the electron beam on a probe.
According to a an embodiment of the invention the magnetic dipole lens comprises dipole coils which are arranged on the yoke of the second magnetic quadrupole lens. By arranging the dipole coils on this second yoke the magnetic dipole field can be directly superimposed to the magnetic quadrupole field of the second quadrupole lens. The second yoke can serve both as a yoke for the second quadrupole lens and as a yoke for the dipole lens. Thereby space can be saved and the length of the entire electron optical apparatus can be reduced. Furthermore the weight for an additional yoke can be saved. According to a further embodiment of the invention the electron optical apparatus comprises a scattered electron collector (SEC). The SEC is adapted to collect backscattered electrons created on the impact of accelerated electrons coming from the electron optical apparatus. The accelerated electrons hit the surface of a probe such as an anode disc of an X-ray emitting device. Some of these electrons are reflected. Other electron free secondary electrons from the probe. All these backscattered electrons fly away from the probe and to the SEC where they are collected. The SEC can be positioned downstream of the second quadrupole lens i.e. at an end of the electron optical apparatus opposite to the cathode. The SEC can be prepared with an electrically conductive material. An electric voltage can be applied to the SEC such that the SEC and the anode are on the same electric potential. For example, the SEC can be electrically connected to the anode. The SEC can have the form of an inverse cup having an opening in a center through which the electron beam can pass. The SEC can be continuous to a bottle neck of the anode cup.
According to a further embodiment of the invention each of the components such as the cathode including the emitter, the anode, the first and the second magnetic quadrupole lenses and the magnetic dipole lens and optionally the scattered electron collector has a symmetry with respect to the optical axis. The components can be arranged co-axially with respect to the optical axis. Using such symmetrical arrangement the design of the electron optical apparatus can be simplified. Furthermore, a defined and symmetric focal spot can be achieved.
According to a further embodiment of the invention the electron optical apparatus has a length along the optical axis of less than 90mm and preferably between 70mm and 90mm. Including the scattered electron collector the length of the electron optical apparatus can be adapted to be no longer than 150mm or preferably between 120mm and 150mm.This short length can be achieved by using flat space saving components such as the flat emitter and by advantageously arranging the components of the apparatus. For example, the magnetic dipole lens can be integrated into the second quadrupole lens thereby saving space in the direction of the optical axis. Having such short length the electron optical apparatus is particularly well suited for applications with space or weight restrictions such as CT or CV applications.
According to a further embodiment of the invention the planar surface of the emitter is non- structured. In other words, the surface of the emitter from which the electrons can be emitted towards the anode is a homogeneous plane without any recesses or protrusions. Electrons can be emitted homogeneously from such non- structured surface. Furthermore, such non-structured emitter surface does not disturb the electric field between the cathode including the emitter and the anode. Especially the electric field close to the surface of the emitter is not disturbed by any structures. Accordingly, electric field lines remain linear and electrons are accelerated parallely to the optical axis without any substantial transversal moving component. The electron beam is not widened. This can help in better focusing of the electron beam.
According to a further embodiment of the invention the planar surface of the emitter is finely structured. In other words, fine structures such as e.g. grooves, slits or recesses are located within the planar surface of the emitter. These fine structures can be used e.g. for confining an electrical current within the emitter which is used to electrically heat the emitter. However, the size and/or arrangement of such fine structures can be chosen such that the emitted electrons are not excessively scattered and such that the electric field is not excessively distorted. According to a further aspect of the invention there is provided an X-ray emitting device comprising the following component along an optical axis: an electron optical apparatus as described above; and an anode disc arranged such that the accelerated electrons impact on a electron receiving surface of the anode disc.
The anode disc can have a slanted surface onto which the electron beam coming from the electron optical apparatus can be directed. Electrons impacting the surface of the anode disc and entering the anode material produce X-ray radiation. The angle of the slanted surface of the anode disc can be selected such that the X-rays are emitted transversely, preferably perpendicularly, to the optical axis of the electron optical apparatus. The anode disc can be prepared with a selected material in order to receive desired X-ray characteristics. The anode disc can be rotated about an axis parallel to the optical axis of the electron optical apparatus.
According to a further embodiment of the invention the electrical anode and the anode disc (=target) are essentially on the same electric potential. In case that a scattered electron collector is provided also this SEC can be set on the electrical potential of the anode. Accordingly, the region between the anode and the anode disc can be free of any electric field. By eliminating any electric field in the proximity of the surface of the anode disc it can be prevented that backscattered electrons coming from the surface of the anode disc are reattracted towards the anode disc. Otherwise, these reattracted backscattered electrons would unnecessarily widen the focal spot and would furthermore contribute to heating of the anode disc thereby increasing the cooling requirements for the anode disc.
According to a further embodiment of the invention the cathode including the emitter, the electrical anode, the first magnetic quadrupole lens, the second magnetic quadrupole lens, the optional scattered electron collector and the anode disc are all connected to a water cooling circuit. A combined water cooling circuit can be used for cooling all component except the cathode including the emitter. The water in the cooling circuit is electrically conductive but when the mentioned components are preferably all on ground potential no further measures for electrically insulating the cooling circuit and the components has to be provided.
According to a further embodiment of the invention a distance from the electron emitting surface of the emitter to a electron receiving surface of the anode disc is less than 150mm and preferably between 120mm and 150mm. As outlined above, this can be achieved by special selection of the constituent component and the arrangement of the components.
According to a further aspect of the invention there is provided a medical X-ray device comprising an X-ray emitting device as outlined above. The medical X- ray device can be for example a computer tomograph or a cardiovascular imaging device. As outlined above such medical devices can have severe requirements in terms of focal spot size, control of the focal spot size, ratio and position, cooling down times and, concerning CTs, gantry rotation times. Using an X-ray emitting device as outlined above these requirements can be met.
According to a further aspect of the invention there is provided a method of creating an electron beam, the method comprising the steps of: emitting electrons from a planar surface of a emitter; accelerating the electrons in a direction essentially parallel to the optical axis using an anode; deflecting the accelerated electrons using a first magnetic quadrupole lens; further deflecting the accelerated electrons using a second magnetic quadrupole lens; further deflecting the accelerated electrons using a magnetic dipole lens. Exemplary embodiments of the present invention are described with reference to an electron optical apparatus or an X-ray emitting device. It has to be pointed out that of course any combination of features relating to different subject matters is also possible and that the features of the apparatus or device can be applied correspondingly to the method according to the invention. It has to be noted that embodiments of the invention are described with reference to different subject matters. In particular, some embodiments are described with reference to apparatus type claims whereas other embodiments are described with reference to method type claims. However, a person skilled in the art will gather from the above and the following description that, unless other notified, in addition to any combination of features belonging to one type of subject matter also any combination between features relating to different subject matters, in particular between features of the apparatus type claims and features of the method type claims is considered to be disclosed with this application.
The aspects defined above and further aspects, features and advantages of the present invention can be derived from the examples of embodiment to be described hereinafter and are explained with reference to the examples of embodiment. The invention will be described in more detail hereinafter with reference to examples of embodiment but to which the invention is not limited. BRIEF DESCRIPTION OF THE DRAWINGS
Fig. Ia shows a schematic setup of an X-ray emitting device according to the present invention in cross-section perpendicular to a width direction.
Fig. Ib shows the schematic setup of Fig Ia in cross-section perpendicular to a length direction.
Fig. 2 shows a magnetic quadrupole lens which can be used as first magnetic quadrupole lens in the setup of Fig. Ia.
Fig. 3 shows a magnetic quadrupole lens including a magnetic dipole lens which can be used as second magnetic quadrupole lens in the setup ofFig. Ia.
Fig. 4 shows a diagram indicating length and width of area-minimized focal spots for different tube currents achievable with an X-ray emitting device according to the invention.
Fig. 5 visualizes different focal spots for CT applications.
Fig. 6 visualizes different focal spot positions achieved by applying specific currents to the magnetic dipole lens of an X-ray emitting device according to the invention.
Fig. 7 schematically shows a computer tomography device according to the invention.
DETAILED DESCRIPTION
The illustration in the drawing is schematically. It is noted that in different figures, similar or identical elements are provided with the same reference signs or with reference signs, which are different from the corresponding reference signs only within the first digit. Future X-ray medical examinations have sophisticated requirements on the spot sizes and shapes in combination with fast changes in positions. Due to the limitations in space of typically 130mm in optical length and an optimal heat management by implementing a SEC, a much better electron optic than usually used in X-ray tubes is necessary.
Fig. Ia and Ib show an embodiment of an X-ray emitting device 1 according to the invention. The proposed X-ray emitting device to reach the above requirements comprises a cathode with a flat emitter 3 as an electron source and a lens system 5.
The objective of spot control is to create a line focus (an elongated spot) on the slanted part of an anode disc 7 in such a way that the effective X-ray source has an approximately equal size in width and length dimension when viewed from an X-ray exit window. To achieve this, the spot length has to be enlarged by a factor (typically around 8) with respect to the width depending on the anode slant angle (typically around 8°).
Both optical parts, cathode with emitter 3 and lens system 5, have to be optimal to fulfill the high requests for new state-of-the-art X-ray tubes. The first essential step is to reduce the tangential energy components of the emitted electrons. This is reached by emitting the electrons from a flat, smooth and unstructured tungsten or tungsten alloy foil emitter within the cathode 3 which is directly heated by an applied electrical current. The emitter 3 has a planar surface 9 directed towards an anode 11. A first pre-focusing element in length and width direction is given by a cathode cup 13 with a ring on high potential. The entrance into the electrical anode opening 15 acts as a second optical element having an isotropic defocusing effect. It has a entrance diameter of typically 20mm and enlarges within a bottle-neck 17 up to 30mm to give room for an uncritical electron beam shaping. The main optical component, the double magnetic quadrupole lens including a first magnetic quadrupole lens 19 and a second magnetic quadrupole lens 21, is positioned approximately in the middle between the cathode 3 and the target anode disc 7 around the bottle-neck 17. It consists of a cathode side first quadrupole lens 19 and an anode side second quadrupole lens 21 with integrated dipole lens 23 enabling a shifting of the focal spot in x/z-direction, i.e. a plane perpendicular to an optical axis 25 of the X-ray device 1. The first magnetic quadrupole lens 19 focuses in length and defocuses in width direction of the focal spot. The electron beam is then focused in width direction and defocused in length direction by the following second quadrupole lens 21. In combination the two sequentially arranged magnetic quadrupole lenses guarantee a net focusing effect in both directions of the focal spot which is also demonstrated in Fig. 1. This mode of operation of the double magnetic quadrupole lens leads to the required narrow line focus on the target anode disc 7 with typical length to width relations between 7 and 10.
Additionally this concept leaves an electrical field- free and hence optical- free region 29 of more than 40% of the total distance between cathode 3 and target anode disc 7 to accommodate a scattered electron collector 31 for the heat management of scattered electrons.
In Fig. Ib, the region (a) indicates an emitting and acceleration length, the region (b) indicates a focusing and beam shaping length and the region (c) indicates a scattered electron collector and heat management length. Fig. 2 shows a top view of the first magnetic quadrupole lens 19. A square yoke 41 comprises protrusions 43 directed to the center of the square. On each of these four protrusions 43 a magnetic coil 45 is provided.
Similarly, Fig. 3 shows a top view of the second magnetic quadrupole lens 21. A square yoke 51 comprises protrusions 53 directed to the center of the square. On each of these four protrusions 53 a magnetic coil 55 is provided. Furthermore, a magnetic coil
57 for forming a magnetic dipole lens 23 is arranged in the center of each of the longitudinal arms of the square yoke 51.
The disclosed setup requires a beam path length of approximately
130mm which is drastically larger than in common bipolar tubes (»20mm) but it still allows the manufacturing of tubes small and light enough to be used for CV- applications and to fit onto common CT-gantries.
The resulting smallest foci using an emission area of 50mm2 are shown in
Fig. 4 as a function of tube current. It is obvious that these foci are outstanding small with respect to the tube currents in comparison to every other X-ray tube used today for medical examinations. Enlarging these minimal focal spots by independently changing length and width at a given tube current can easily be done by only controlling the coil currents of the two magnetic quadrupole lenses 19, 21.
Experiments have been performed to investigate how strong the influence of the electron emitting emitter on the optical properties is. With an X-ray emitting device using an emitter having an unstructured emitting surface of 50mm2 a focal spot width of 0.2mm and a focal spot length of 0.23mm could be obtained. With an X-ray emitting device using an emitter having a slightly structured emitting surface of 50mm2 with 20x40μm slits in width direction, a focal spot width of 0.3mm and a focal spot length of 0.46mm could be obtained. Using the fine structured emitter having the same emission area like the unstructured one but using a meander design with 20 slits of
40 μm in width to create a current path leads to significantly larger spot sizes. The focal spot width enlarges by 50% and the focal spot length by 100% for the smallest spot. The stronger influence on the length is caused by electrons emitting from the inner slit walls which are orientated in width direction. For a commonly used coil emitter this effect even drastically increases:
The smallest projected focal spot area (0.513x0.946mm2 = 0.485mm2 for 8° slant angle) for a tube current of only 24OmA and 12OkV is more than ten times compared to the unstructured emitter setup.
To further demonstrate the possibilities of the electron optical concept, three focal spots adjusted to sizes for near future CV and CT applications are shown in Fig. 5. Fig. 5a shows a IEC 03 focal spot for CV applications; Fig. 5b shows a 0.75x0.9mm2 focal spot for CT applications; and Fig. 5c shows a 1.30x1.45mm2 focal spot for CT applications.
Shifted focal spots by means of the dipoles integrated on the second yoke in X and Z-direction are shown in Fig. 6.
Finally, Fig. 7 shows a computer tomography apparatus 100, which is also called a CT scanner and in which the above X-ray emitting device can be used. The CT scanner 100 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 105 designates a source of radiation such as an X-ray emitting device as described above, which emits polychromatic radiation 107. The CT scanner 100 further comprises an aperture system 106, which forms the X-radiation being emitted from the X-ray source 105 into a radiation beam 107. The spectral distribution of the radiation beam emitted from the radiation source 105 may further be changed by a filter element (not shown), which is arranged close to the aperture system 106.
The radiation beam 107, which may by a cone-shaped or a fan-shaped beam 107, is directed such that it penetrates a region of interest 110a such as a head 11 Oa of a patient 110.
The patient 110 is positioned on a table 112. The patient's head 110a is arranged in a central region of the gantry 101, which central region represents the examination region of the CT scanner 100. After penetrating the region of interest 110a the radiation beam 107 impinges onto a radiation detector 115. In order to be able to suppress X-radiation being scattered by the patient's head 110a and impinging onto the X-ray detector under an oblique angle there is provided a not depicted anti scatter grid. The anti scatter grid is preferably positioned directly in front of the detector 115.
The X-ray detector 115 is arranged on the gantry 101 opposite to the X- ray tube 105. The detector 115 comprises a plurality of detector elements 115a wherein each detector element 115a is capable of detecting X-ray photons, which have been passed through the head 110a of the patient 110. During scanning the region of interest 110a, the X-ray source 105, the aperture system 106 and the detector 115 are rotated together with the gantry 101 in a rotation direction indicated by an arrow 117. For rotation of the gantry 101, the motor 103 is connected to a motor control unit 120, which itself is connected to a data processing device 125. The data processing device 125 includes a reconstruction unit, which may be realized by means of hardware and/or by means of software. The reconstruction unit is adapted to reconstruct a 3D image based on a plurality of 2D images obtained under various observation angles.
Furthermore, the data processing device 125 serves also as a control unit, which communicates with the motor control unit 120 in order to coordinate the movement of the gantry 101 with the movement of the table 112. A linear displacement of the table 112 is carried out by a motor 113, which is also connected to the motor control unit 120.
During operation of the CT scanner 100 the gantry 101 rotates and in the same time the table 112 is shifted linearly parallel to the rotational axis 102 such that a helical scan of the region of interest 110a is performed. It should be noted that 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. Thereby, slices of the head 110a may be measured with high accuracy. A larger three-dimensional representation of the patient's head may be obtained by sequentially moving the table 112 in discrete steps parallel to the rotational axis 102 after at least one half gantry rotation has been performed for each discrete table position.
The detector 115 is coupled to a pre-amplifϊer 118, which itself is coupled to the data processing device 125. The processing device 125 is capable, based on a plurality of different X-ray projection datasets, which have been acquired at different projection angles, to reconstruct a 3D representation of the patient's head 110a. In order to observe the reconstructed 3D representation of the patient's head 110a a display 126 is provided, which is coupled to the data processing device
125. Additionally, arbitrary slices of a perspective view of the 3D representation may also be printed out by a printer 127, which is also coupled to the data processing device
125. Further, the data processing device 125 may also be coupled to a picture archiving and communications system 128 (PACS).
It should be noted that the monitor 126, the printer 127 and/or other devices supplied within the CT scanner 100 might be arranged local to the computer tomography apparatus 100. Alternatively, these components may be remote from the
CT scanner 100, such as elsewhere within an institution or hospital, or in an entirely different location linked to the CT scanner 100 via one ore more configurable networks, such as the Internet, virtual private networks and so forth.
Summarising all facts discussed above, it is pointed out that the proposed new electron optical concept, comprising a flat unstructured or even fine-structured flat emitter and two magnetic quadrupole lenses, provides all features necessary for medical X-ray examinations without exceeding geometrical space and weight restrictions due to its small size. The electron optical concept comprises a non-structured or fine structured thin flat emitter and a magnetic double quadrupole lens with dipole coils on the anode- side yoke within a length of 70-90mm and a total optical length from emitter to target between 120mm and 150mm. The 50-60mm in length between the double quadrupole lens and the target are lens-free and could comprise a scattered-electron-collector (SEC).
This concept can provide e.g. focal spots variable in width between 0.2- 1.3mm with arbitrary values in focal spot length between 0.23- 1.45mm for tube currents of 100-160OmA and high voltages of 70-14OkV necessary for medical X-ray applications. Additionally it is possible to quickly shift these foci in radial and tangential direction which leads to higher spatial resolutions.
The invention would be applicable to any field in which electrons have to be focused with variable focal spot sizes, shapes and positions combined with high currents but only a limited space for optical elements is available.
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 should not be construed as limiting the scope of the claims.
In order to recapitulate the above described embodiments of the present invention one can state: To fulfill the high electron-optical demands for high-end X-ray tubes, a better concept than used in standard tubes is necessary. A solution to reach this is given by the combination of a flat electron emitter and a magnetic double quadrupole with integrated magnetic dipoles. This setup can be realised within an optical length of approximately 130mm with all focusing elements within the emitter half and is therefore practicable for high-end tubes for CV and CT applications. This electron- optical concept provides the following advantages: 1) focusing high current electron beams into the required line shaped small focal spots with a typical ratio of 7-10 between length and width perpendicular to the optical axis, 2) retaining focusing properties over a large range of kV and mA, 3) independent control of focal spot width and length, and 4) active control of focal spot size and position.

Claims

oCLAIMS:
1. An electron optical apparatus (1) comprising the following components along an optical axis (25): a cathode including an emitter (3), wherein the emitter has a substantially planar surface (9) for emitting electrons; an anode (11) for accelerating the emitted electrons in a direction essentially along the optical axis (25); a first magnetic quadrupole lens (19) for deflecting the accelerated electrons and having a first yoke (41); a second magnetic quadrupole lens (21) for further deflecting the accelerated electrons and having a second yoke (51); and a magnetic dipole lens (23) for further deflecting the accelerated electrons.
2. The apparatus according to claim 1, wherein the magnetic dipole lens (23) comprises dipole coils (57) arranged on the second yoke(51).
3. The apparatus according to claim 1 or 2, further comprising a scattered- electron-collector (31).
4. The apparatus according to one of claims 1 to 3, wherein each of the components has a symmetry with respect to the optical axis (25) and wherein the components are arranged co-axially with respect to the optical axis (25).
5. The apparatus according to one of claims 1 to 4, wherein the apparatus (1) has a length along the optical axis (25) of less than 90mm.
6. The apparatus according to one of claims 1 to 5, wherein the planar surface (9) of the emitter (3) is non-structured.
7. The apparatus according to one of claims 1 to 5, wherein the planar surface (9) of the emitter (3) is finely structured.
8. An X-ray emitting device comprising the following components along an optical axis (25): an electron optical apparatus (1) according to one of claims 1 to 7; and an anode disc (7) arranged such that the accelerated electrons impact on an electron receiving surface of the anode disc (7).
9. The X-ray emitting device according to claim 8, wherein the anode (11) and the anode disc (7) are essentially on the same electric potential.
10. The X-ray emitting device according to claim 8 or 9, wherein the anode (11), the first magnetic quadrupole lens (19), the second magnetic quadrupole lens (21), the optional scattered electron collector (31) and the anode disc (7) are all connected to a water cooling circuit.
11. The X-ray emitting device according to one of claims 8 to 10, wherein a distance from the electron emitting surface (9) of the emitter (3) to the electron receiving surface of the anode disc (7) is less than 150mm.
12. A medical X-ray device comprising an X-ray emitting device according to one of claims 8 to 11.
13. A method of creating an electron beam, the method comprising the steps of: emitting electrons from a planar surface (9) of an emitter (3); accelerating the electrons in a direction essentially parallel to an optical axis (25) using an anode (11); deflecting the accelerated electrons using a first magnetic quadrupole lens (19); further deflecting the accelerated electrons using a second magnetic quadrupole lens (21); further deflecting the accelerated electrons using a magnetic dipole lens
(23).
PCT/IB2007/054087 2006-10-13 2007-10-08 Electron optical apparatus, x-ray emitting device and method of producing an electron beam WO2008044194A2 (en)

Priority Applications (4)

Application Number Priority Date Filing Date Title
AT07826677T ATE496389T1 (en) 2006-10-13 2007-10-08 X-RAY EMISSION DEVICE AND METHOD FOR PRODUCING AN ELECTRON BEAM FOR GENERATING AN X-RAY BEAM IN AN X-RAY EMISSION DEVICE
DE602007012126T DE602007012126D1 (en) 2006-10-13 2007-10-08 X-RAY MISSION DEVICE AND METHOD OF TORQUE X-RAY IN AN X-RAY MISSION DEVICE
EP07826677A EP2074642B1 (en) 2006-10-13 2007-10-08 X-ray emitting device and method of producing an electron beam to produce x-ray radiation in an x-ray emitting device
US12/444,745 US7839979B2 (en) 2006-10-13 2007-10-08 Electron optical apparatus, X-ray emitting device and method of producing an electron beam

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
EP06122223.8 2006-10-13
EP06122223 2006-10-13

Publications (2)

Publication Number Publication Date
WO2008044194A2 true WO2008044194A2 (en) 2008-04-17
WO2008044194A3 WO2008044194A3 (en) 2008-06-12

Family

ID=39156142

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/IB2007/054087 WO2008044194A2 (en) 2006-10-13 2007-10-08 Electron optical apparatus, x-ray emitting device and method of producing an electron beam

Country Status (6)

Country Link
US (1) US7839979B2 (en)
EP (1) EP2074642B1 (en)
CN (2) CN101523544A (en)
AT (1) ATE496389T1 (en)
DE (1) DE602007012126D1 (en)
WO (1) WO2008044194A2 (en)

Cited By (97)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2009142548A2 (en) * 2008-05-22 2009-11-26 Vladimir Yegorovich Balakin X-ray method and apparatus used in conjunction with a charged particle cancer therapy system
WO2010058330A1 (en) * 2008-11-21 2010-05-27 Philips Intellectual Property & Standards Gmbh X-ray tube with switchable grid for gating of electron beam current during voltage breakdown
WO2011018729A1 (en) * 2009-08-13 2011-02-17 Koninklijke Philips Electronics N.V. X-ray tube with independent x- and z- dynamic focal spot deflection
US7943913B2 (en) 2008-05-22 2011-05-17 Vladimir Balakin Negative ion source method and apparatus used in conjunction with a charged particle cancer therapy system
US7953205B2 (en) 2008-05-22 2011-05-31 Vladimir Balakin Synchronized X-ray / breathing method and apparatus used in conjunction with a charged particle cancer therapy system
WO2011083416A1 (en) * 2010-01-08 2011-07-14 Koninklijke Philips Electronics N.V. X-ray tube with a combined x- and y- focal spot deflection method
US8067748B2 (en) 2008-05-22 2011-11-29 Vladimir Balakin Charged particle beam acceleration and extraction method and apparatus used in conjunction with a charged particle cancer therapy system
US8089054B2 (en) 2008-05-22 2012-01-03 Vladimir Balakin Charged particle beam acceleration and extraction method and apparatus used in conjunction with a charged particle cancer therapy system
US8093564B2 (en) 2008-05-22 2012-01-10 Vladimir Balakin Ion beam focusing lens method and apparatus used in conjunction with a charged particle cancer therapy system
US8129694B2 (en) 2008-05-22 2012-03-06 Vladimir Balakin Negative ion beam source vacuum method and apparatus used in conjunction with a charged particle cancer therapy system
US8129699B2 (en) 2008-05-22 2012-03-06 Vladimir Balakin Multi-field charged particle cancer therapy method and apparatus coordinated with patient respiration
US8144832B2 (en) 2008-05-22 2012-03-27 Vladimir Balakin X-ray tomography method and apparatus used in conjunction with a charged particle cancer therapy system
US8178859B2 (en) 2008-05-22 2012-05-15 Vladimir Balakin Proton beam positioning verification method and apparatus used in conjunction with a charged particle cancer therapy system
US8188688B2 (en) 2008-05-22 2012-05-29 Vladimir Balakin Magnetic field control method and apparatus used in conjunction with a charged particle cancer therapy system
US8198607B2 (en) 2008-05-22 2012-06-12 Vladimir Balakin Tandem accelerator method and apparatus used in conjunction with a charged particle cancer therapy system
US8229072B2 (en) 2008-07-14 2012-07-24 Vladimir Balakin Elongated lifetime X-ray method and apparatus used in conjunction with a charged particle cancer therapy system
US8288742B2 (en) 2008-05-22 2012-10-16 Vladimir Balakin Charged particle cancer therapy patient positioning method and apparatus
US8309941B2 (en) 2008-05-22 2012-11-13 Vladimir Balakin Charged particle cancer therapy and patient breath monitoring method and apparatus
US8368038B2 (en) 2008-05-22 2013-02-05 Vladimir Balakin Method and apparatus for intensity control of a charged particle beam extracted from a synchrotron
US8373145B2 (en) 2008-05-22 2013-02-12 Vladimir Balakin Charged particle cancer therapy system magnet control method and apparatus
US8373143B2 (en) 2008-05-22 2013-02-12 Vladimir Balakin Patient immobilization and repositioning method and apparatus used in conjunction with charged particle cancer therapy
US8374314B2 (en) 2008-05-22 2013-02-12 Vladimir Balakin Synchronized X-ray / breathing method and apparatus used in conjunction with a charged particle cancer therapy system
US8373146B2 (en) 2008-05-22 2013-02-12 Vladimir Balakin RF accelerator method and apparatus used in conjunction with a charged particle cancer therapy system
KR101233862B1 (en) * 2008-05-22 2013-02-15 블라디미르 예고르비치 발라킨 X―ray method and apparatus used in conjunction with a charged particle cancer therapy system
US8378321B2 (en) 2008-05-22 2013-02-19 Vladimir Balakin Charged particle cancer therapy and patient positioning method and apparatus
US8378311B2 (en) 2008-05-22 2013-02-19 Vladimir Balakin Synchrotron power cycling apparatus and method of use thereof
US8399866B2 (en) 2008-05-22 2013-03-19 Vladimir Balakin Charged particle extraction apparatus and method of use thereof
US8436327B2 (en) 2008-05-22 2013-05-07 Vladimir Balakin Multi-field charged particle cancer therapy method and apparatus
US8519365B2 (en) 2008-05-22 2013-08-27 Vladimir Balakin Charged particle cancer therapy imaging method and apparatus
US8569717B2 (en) 2008-05-22 2013-10-29 Vladimir Balakin Intensity modulated three-dimensional radiation scanning method and apparatus
US8598543B2 (en) 2008-05-22 2013-12-03 Vladimir Balakin Multi-axis/multi-field charged particle cancer therapy method and apparatus
US8624528B2 (en) 2008-05-22 2014-01-07 Vladimir Balakin Method and apparatus coordinating synchrotron acceleration periods with patient respiration periods
US8625739B2 (en) 2008-07-14 2014-01-07 Vladimir Balakin Charged particle cancer therapy x-ray method and apparatus
US8627822B2 (en) 2008-07-14 2014-01-14 Vladimir Balakin Semi-vertical positioning method and apparatus used in conjunction with a charged particle cancer therapy system
US8637833B2 (en) 2008-05-22 2014-01-28 Vladimir Balakin Synchrotron power supply apparatus and method of use thereof
US8642978B2 (en) 2008-05-22 2014-02-04 Vladimir Balakin Charged particle cancer therapy dose distribution method and apparatus
US8710462B2 (en) 2008-05-22 2014-04-29 Vladimir Balakin Charged particle cancer therapy beam path control method and apparatus
US8718231B2 (en) 2008-05-22 2014-05-06 Vladimir Balakin X-ray tomography method and apparatus used in conjunction with a charged particle cancer therapy system
US8791435B2 (en) 2009-03-04 2014-07-29 Vladimir Egorovich Balakin Multi-field charged particle cancer therapy method and apparatus
US8841866B2 (en) 2008-05-22 2014-09-23 Vladimir Yegorovich Balakin Charged particle beam extraction method and apparatus used in conjunction with a charged particle cancer therapy system
US8896239B2 (en) 2008-05-22 2014-11-25 Vladimir Yegorovich Balakin Charged particle beam injection method and apparatus used in conjunction with a charged particle cancer therapy system
US8901509B2 (en) 2008-05-22 2014-12-02 Vladimir Yegorovich Balakin Multi-axis charged particle cancer therapy method and apparatus
US8907309B2 (en) 2009-04-17 2014-12-09 Stephen L. Spotts Treatment delivery control system and method of operation thereof
US8933651B2 (en) 2012-11-16 2015-01-13 Vladimir Balakin Charged particle accelerator magnet apparatus and method of use thereof
US8957396B2 (en) 2008-05-22 2015-02-17 Vladimir Yegorovich Balakin Charged particle cancer therapy beam path control method and apparatus
US8963112B1 (en) 2011-05-25 2015-02-24 Vladimir Balakin Charged particle cancer therapy patient positioning method and apparatus
US8969834B2 (en) 2008-05-22 2015-03-03 Vladimir Balakin Charged particle therapy patient constraint apparatus and method of use thereof
US8975600B2 (en) 2008-05-22 2015-03-10 Vladimir Balakin Treatment delivery control system and method of operation thereof
US9044600B2 (en) 2008-05-22 2015-06-02 Vladimir Balakin Proton tomography apparatus and method of operation therefor
US9058910B2 (en) 2008-05-22 2015-06-16 Vladimir Yegorovich Balakin Charged particle beam acceleration method and apparatus as part of a charged particle cancer therapy system
US9056199B2 (en) 2008-05-22 2015-06-16 Vladimir Balakin Charged particle treatment, rapid patient positioning apparatus and method of use thereof
US9095040B2 (en) 2008-05-22 2015-07-28 Vladimir Balakin Charged particle beam acceleration and extraction method and apparatus used in conjunction with a charged particle cancer therapy system
US9155911B1 (en) 2008-05-22 2015-10-13 Vladimir Balakin Ion source method and apparatus used in conjunction with a charged particle cancer therapy system
US9168392B1 (en) 2008-05-22 2015-10-27 Vladimir Balakin Charged particle cancer therapy system X-ray apparatus and method of use thereof
US9177751B2 (en) 2008-05-22 2015-11-03 Vladimir Balakin Carbon ion beam injector apparatus and method of use thereof
DE102014211694A1 (en) * 2014-06-18 2015-12-24 Siemens Aktiengesellschaft X-ray tube
WO2016144897A1 (en) * 2013-10-29 2016-09-15 Varian Medical Systems, Inc. X-ray tube having magnetic quadrupoles for focusing and magnetic dipoles for steering
US9498649B2 (en) 2008-05-22 2016-11-22 Vladimir Balakin Charged particle cancer therapy patient constraint apparatus and method of use thereof
US9579525B2 (en) 2008-05-22 2017-02-28 Vladimir Balakin Multi-axis charged particle cancer therapy method and apparatus
US9616252B2 (en) 2008-05-22 2017-04-11 Vladimir Balakin Multi-field cancer therapy apparatus and method of use thereof
US9682254B2 (en) 2008-05-22 2017-06-20 Vladimir Balakin Cancer surface searing apparatus and method of use thereof
US9737731B2 (en) 2010-04-16 2017-08-22 Vladimir Balakin Synchrotron energy control apparatus and method of use thereof
US9737272B2 (en) 2008-05-22 2017-08-22 W. Davis Lee Charged particle cancer therapy beam state determination apparatus and method of use thereof
US9737734B2 (en) 2008-05-22 2017-08-22 Susan L. Michaud Charged particle translation slide control apparatus and method of use thereof
US9737733B2 (en) 2008-05-22 2017-08-22 W. Davis Lee Charged particle state determination apparatus and method of use thereof
US9744380B2 (en) 2008-05-22 2017-08-29 Susan L. Michaud Patient specific beam control assembly of a cancer therapy apparatus and method of use thereof
US9782140B2 (en) 2008-05-22 2017-10-10 Susan L. Michaud Hybrid charged particle / X-ray-imaging / treatment apparatus and method of use thereof
CN107408481A (en) * 2015-03-09 2017-11-28 万睿视影像有限公司 X-ray tube with the magnetic quadrupole for focusing and the magnetic dipole for steering
US9855444B2 (en) 2008-05-22 2018-01-02 Scott Penfold X-ray detector for proton transit detection apparatus and method of use thereof
US9907981B2 (en) 2016-03-07 2018-03-06 Susan L. Michaud Charged particle translation slide control apparatus and method of use thereof
US9910166B2 (en) 2008-05-22 2018-03-06 Stephen L. Spotts Redundant charged particle state determination apparatus and method of use thereof
US9937362B2 (en) 2008-05-22 2018-04-10 W. Davis Lee Dynamic energy control of a charged particle imaging/treatment apparatus and method of use thereof
US9974978B2 (en) 2008-05-22 2018-05-22 W. Davis Lee Scintillation array apparatus and method of use thereof
US9981147B2 (en) 2008-05-22 2018-05-29 W. Davis Lee Ion beam extraction apparatus and method of use thereof
US10029124B2 (en) 2010-04-16 2018-07-24 W. Davis Lee Multiple beamline position isocenterless positively charged particle cancer therapy apparatus and method of use thereof
US10029122B2 (en) 2008-05-22 2018-07-24 Susan L. Michaud Charged particle—patient motion control system apparatus and method of use thereof
US10037863B2 (en) 2016-05-27 2018-07-31 Mark R. Amato Continuous ion beam kinetic energy dissipater apparatus and method of use thereof
US10070831B2 (en) 2008-05-22 2018-09-11 James P. Bennett Integrated cancer therapy—imaging apparatus and method of use thereof
US10086214B2 (en) 2010-04-16 2018-10-02 Vladimir Balakin Integrated tomography—cancer treatment apparatus and method of use thereof
US10092776B2 (en) 2008-05-22 2018-10-09 Susan L. Michaud Integrated translation/rotation charged particle imaging/treatment apparatus and method of use thereof
EP3396696A1 (en) * 2017-04-27 2018-10-31 Imatrex, Inc. Compact deflecting magnet
US10143854B2 (en) 2008-05-22 2018-12-04 Susan L. Michaud Dual rotation charged particle imaging / treatment apparatus and method of use thereof
US10179250B2 (en) 2010-04-16 2019-01-15 Nick Ruebel Auto-updated and implemented radiation treatment plan apparatus and method of use thereof
US10349906B2 (en) 2010-04-16 2019-07-16 James P. Bennett Multiplexed proton tomography imaging apparatus and method of use thereof
US10376717B2 (en) 2010-04-16 2019-08-13 James P. Bennett Intervening object compensating automated radiation treatment plan development apparatus and method of use thereof
US10460899B2 (en) 2014-10-06 2019-10-29 Koninklijke Philips N.V. Modification arrangement for an X-ray generating device
US10518109B2 (en) 2010-04-16 2019-12-31 Jillian Reno Transformable charged particle beam path cancer therapy apparatus and method of use thereof
US10548551B2 (en) 2008-05-22 2020-02-04 W. Davis Lee Depth resolved scintillation detector array imaging apparatus and method of use thereof
US10556126B2 (en) 2010-04-16 2020-02-11 Mark R. Amato Automated radiation treatment plan development apparatus and method of use thereof
US10555710B2 (en) 2010-04-16 2020-02-11 James P. Bennett Simultaneous multi-axes imaging apparatus and method of use thereof
US10589128B2 (en) 2010-04-16 2020-03-17 Susan L. Michaud Treatment beam path verification in a cancer therapy apparatus and method of use thereof
US10625097B2 (en) 2010-04-16 2020-04-21 Jillian Reno Semi-automated cancer therapy treatment apparatus and method of use thereof
US10638988B2 (en) 2010-04-16 2020-05-05 Scott Penfold Simultaneous/single patient position X-ray and proton imaging apparatus and method of use thereof
US10684380B2 (en) 2008-05-22 2020-06-16 W. Davis Lee Multiple scintillation detector array imaging apparatus and method of use thereof
US10751551B2 (en) 2010-04-16 2020-08-25 James P. Bennett Integrated imaging-cancer treatment apparatus and method of use thereof
US11648420B2 (en) 2010-04-16 2023-05-16 Vladimir Balakin Imaging assisted integrated tomography—cancer treatment apparatus and method of use thereof
TWI820158B (en) * 2018-06-25 2023-11-01 瑞典商艾希凜有限公司 X-ray source for emitting x-ray radiation and method for generating x-ray radiation

Families Citing this family (59)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7963695B2 (en) 2002-07-23 2011-06-21 Rapiscan Systems, Inc. Rotatable boom cargo scanning system
BR0315831A (en) 2002-11-04 2005-09-13 Procter & Gamble Liquid striped personal care composition containing a cleaning phase and a separate benefit phase with improved stability
US7123684B2 (en) 2002-11-27 2006-10-17 Hologic, Inc. Full field mammography with tissue exposure control, tomosynthesis, and dynamic field of view processing
US7616801B2 (en) 2002-11-27 2009-11-10 Hologic, Inc. Image handling and display in x-ray mammography and tomosynthesis
US10638994B2 (en) 2002-11-27 2020-05-05 Hologic, Inc. X-ray mammography with tomosynthesis
EP1816965B1 (en) 2004-11-26 2016-06-29 Hologic, Inc. Integrated multi-mode mammography/tomosynthesis x-ray system
EP1874408A1 (en) 2005-04-13 2008-01-09 The Procter and Gamble Company Mild, structured, multiphase personal cleansing compositions
US7471764B2 (en) 2005-04-15 2008-12-30 Rapiscan Security Products, Inc. X-ray imaging system having improved weather resistance
WO2009142545A2 (en) * 2008-05-22 2009-11-26 Vladimir Yegorovich Balakin Charged particle cancer therapy patient positioning method and apparatus
CA2725498C (en) * 2008-05-22 2015-06-30 Vladimir Yegorovich Balakin Multi-field charged particle cancer therapy method and apparatus
EP2352431B1 (en) * 2008-11-24 2018-08-15 Hologic, Inc. Method and system for controlling x-ray focal spot characteristics for tomosynthesis and mammography imaging
US8515005B2 (en) * 2009-11-23 2013-08-20 Hologic Inc. Tomosynthesis with shifting focal spot and oscillating collimator blades
DE102009047866B4 (en) 2009-09-30 2022-10-06 Siemens Healthcare Gmbh X-ray tube with a backscattered electron collector
US8295442B2 (en) * 2010-07-28 2012-10-23 General Electric Company Apparatus and method for magnetic control of an electron beam
US9504135B2 (en) * 2010-07-28 2016-11-22 General Electric Company Apparatus and method for magnetic control of an electron beam
US8284901B2 (en) 2010-10-26 2012-10-09 General Electric Company Apparatus and method for improved transient response in an electromagnetically controlled x-ray tube
US8385507B2 (en) 2010-10-26 2013-02-26 General Electric Company Apparatus and method for improved transient response in an electromagnetically controlled X-ray tube
US8284900B2 (en) 2010-10-26 2012-10-09 General Electric Company Apparatus and method for improved transient response in an electromagnetically controlled X-ray tube
US8280007B2 (en) 2010-10-26 2012-10-02 General Electric Company Apparatus and method for improved transient response in an electromagnetically controlled X-ray tube
WO2012080958A2 (en) * 2010-12-16 2012-06-21 Koninklijke Philips Electronics N.V. Anode disk element with refractory interlayer and vps focal track
US8515012B2 (en) 2011-01-07 2013-08-20 General Electric Company X-ray tube with high speed beam steering electromagnets
US8542801B2 (en) * 2011-01-07 2013-09-24 General Electric Company X-ray tube with secondary discharge attenuation
DE102011075453A1 (en) * 2011-05-06 2012-11-08 Siemens Aktiengesellschaft X-ray tube and method for operating an X-ray tube
EP2742779B1 (en) * 2011-06-09 2017-04-26 Rapiscan Systems, Inc. System and method for x-ray source weight reduction
US9218933B2 (en) * 2011-06-09 2015-12-22 Rapidscan Systems, Inc. Low-dose radiographic imaging system
US8712015B2 (en) 2011-08-31 2014-04-29 General Electric Company Electron beam manipulation system and method in X-ray sources
US9111331B2 (en) 2011-09-07 2015-08-18 Rapiscan Systems, Inc. X-ray inspection system that integrates manifest data with imaging/detection processing
KR101415025B1 (en) * 2011-11-15 2014-07-07 삼성전자주식회사 X-ray generator and X-ray photograph apparatus
WO2014064748A1 (en) * 2012-10-22 2014-05-01 株式会社島津製作所 X-ray tube device
US9208986B2 (en) 2012-11-08 2015-12-08 General Electric Company Systems and methods for monitoring and controlling an electron beam
US8934603B2 (en) 2013-03-13 2015-01-13 Morpho Detection, Llc Systems and methods for detecting contraband using quadrupole resonance and X-ray detection
MX2016001000A (en) 2013-07-23 2016-08-03 Rapiscan Systems Inc Methods for improving processing speed for object inspection.
WO2015105541A1 (en) * 2013-09-19 2015-07-16 Rapiscan Systems, Inc. Low-dose radiographic inspection system
US9153409B2 (en) 2013-10-23 2015-10-06 General Electric Company Coupled magnet currents for magnetic focusing
CN103578886B (en) * 2013-11-12 2016-08-17 陆振民 electromagnetic wave generating device
DE102013223787A1 (en) 2013-11-21 2015-05-21 Siemens Aktiengesellschaft X-ray tube
US10228487B2 (en) 2014-06-30 2019-03-12 American Science And Engineering, Inc. Rapidly relocatable modular cargo container scanner
US10345479B2 (en) 2015-09-16 2019-07-09 Rapiscan Systems, Inc. Portable X-ray scanner
GB2595986A (en) 2016-02-22 2021-12-15 Rapiscan Systems Inc Systems and methods for detecting threats and contraband in cargo
US11076820B2 (en) 2016-04-22 2021-08-03 Hologic, Inc. Tomosynthesis with shifting focal spot x-ray system using an addressable array
US11380510B2 (en) * 2016-05-16 2022-07-05 Nano-X Imaging Ltd. X-ray tube and a controller thereof
EP3485705A4 (en) 2016-07-14 2020-08-12 Rapiscan Systems, Inc. Systems and methods for improving penetration of radiographic scanners
JP7271425B2 (en) * 2016-09-09 2023-05-11 ボード オブ リージェンツ，ザ ユニバーシティ オブ テキサス システム Apparatus and method for magnetic control of illuminating electron beam
CN110199373B (en) 2017-01-31 2021-09-28 拉皮斯坎系统股份有限公司 High power X-ray source and method of operation
US11707244B2 (en) 2017-08-16 2023-07-25 Hologic, Inc. Techniques for breast imaging patient motion artifact compensation
EP3449835B1 (en) 2017-08-22 2023-01-11 Hologic, Inc. Computed tomography system and method for imaging multiple anatomical targets
CN111225652A (en) 2017-10-20 2020-06-02 宝洁公司 Aerosol foam skin cleaning agent
CN108461370B (en) * 2018-02-07 2020-04-21 叶华伟 Multi-focus double-contrast bulb tube and control method thereof
US11090017B2 (en) 2018-09-13 2021-08-17 Hologic, Inc. Generating synthesized projection images for 3D breast tomosynthesis or multi-mode x-ray breast imaging
CN109119312B (en) * 2018-09-30 2024-06-25 麦默真空技术无锡有限公司 Magnetic scanning type X-ray tube
EP3832689A3 (en) 2019-12-05 2021-08-11 Hologic, Inc. Systems and methods for improved x-ray tube life
US11212902B2 (en) 2020-02-25 2021-12-28 Rapiscan Systems, Inc. Multiplexed drive systems and methods for a multi-emitter X-ray source
US11471118B2 (en) 2020-03-27 2022-10-18 Hologic, Inc. System and method for tracking x-ray tube focal spot position
US11193898B1 (en) 2020-06-01 2021-12-07 American Science And Engineering, Inc. Systems and methods for controlling image contrast in an X-ray system
JP2024509509A (en) 2021-02-23 2024-03-04 ラピスカン システムズ、インコーポレイテッド Systems and methods for eliminating crosstalk signals in one or more scanning systems with multiple x-ray sources
US11961694B2 (en) 2021-04-23 2024-04-16 Carl Zeiss X-ray Microscopy, Inc. Fiber-optic communication for embedded electronics in x-ray generator
US12035451B2 (en) * 2021-04-23 2024-07-09 Carl Zeiss X-Ray Microscopy Inc. Method and system for liquid cooling isolated x-ray transmission target
US11864300B2 (en) 2021-04-23 2024-01-02 Carl Zeiss X-ray Microscopy, Inc. X-ray source with liquid cooled source coils
US11786191B2 (en) 2021-05-17 2023-10-17 Hologic, Inc. Contrast-enhanced tomosynthesis with a copper filter

Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2002099834A2 (en) 2001-06-01 2002-12-12 Koninklijke Philips Electronics N.V. Spot optimization in a color display tube system

Family Cites Families (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB1329412A (en) * 1969-09-18 1973-09-05 Science Res Council Electrical coils for generating magnetic fields
IN167955B (en) * 1986-03-27 1991-01-12 Nokia Data Systems
JPH01151141A (en) 1987-12-08 1989-06-13 Toshiba Corp X-ray tube device
EP0421523B1 (en) * 1989-10-02 1995-06-28 Koninklijke Philips Electronics N.V. Colour display tube system with reduced spot growth
EP0507383B1 (en) 1991-04-04 1995-06-28 Koninklijke Philips Electronics N.V. Colour display tube system
JPH0567442A (en) 1991-09-06 1993-03-19 Toshiba Corp X-ray tube
US5682412A (en) * 1993-04-05 1997-10-28 Cardiac Mariners, Incorporated X-ray source
TW414912B (en) * 1997-04-04 2000-12-11 Matsushita Electronics Corp Color picture tube device
DE19820243A1 (en) * 1998-05-06 1999-11-11 Siemens Ag X=ray tube with variable sized X=ray focal spot and focus switching
DE19903872C2 (en) * 1999-02-01 2000-11-23 Siemens Ag X-ray tube with spring focus for enlarged resolution
GB9906886D0 (en) * 1999-03-26 1999-05-19 Bede Scient Instr Ltd Method and apparatus for prolonging the life of an X-ray target
DE10025807A1 (en) * 2000-05-24 2001-11-29 Philips Corp Intellectual Pty X-ray tube with flat cathode
DE10135995C2 (en) * 2001-07-24 2003-10-30 Siemens Ag Directly heated thermionic flat emitter
CA2464712A1 (en) * 2002-01-31 2003-08-07 The Johns Hopkins University X-ray source and method for producing selectable x-ray wavelength
DE102005041923A1 (en) 2005-09-03 2007-03-08 Comet Gmbh Device for generating X-ray or XUV radiation

Patent Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2002099834A2 (en) 2001-06-01 2002-12-12 Koninklijke Philips Electronics N.V. Spot optimization in a color display tube system

Cited By (126)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9095040B2 (en) 2008-05-22 2015-07-28 Vladimir Balakin Charged particle beam acceleration and extraction method and apparatus used in conjunction with a charged particle cancer therapy system
US8941084B2 (en) 2008-05-22 2015-01-27 Vladimir Balakin Charged particle cancer therapy dose distribution method and apparatus
WO2009142548A3 (en) * 2008-05-22 2010-08-26 Vladimir Yegorovich Balakin X-ray method and apparatus used in conjunction with a charged particle cancer therapy system
US10684380B2 (en) 2008-05-22 2020-06-16 W. Davis Lee Multiple scintillation detector array imaging apparatus and method of use thereof
US7943913B2 (en) 2008-05-22 2011-05-17 Vladimir Balakin Negative ion source method and apparatus used in conjunction with a charged particle cancer therapy system
US7953205B2 (en) 2008-05-22 2011-05-31 Vladimir Balakin Synchronized X-ray / breathing method and apparatus used in conjunction with a charged particle cancer therapy system
US10548551B2 (en) 2008-05-22 2020-02-04 W. Davis Lee Depth resolved scintillation detector array imaging apparatus and method of use thereof
US8067748B2 (en) 2008-05-22 2011-11-29 Vladimir Balakin Charged particle beam acceleration and extraction method and apparatus used in conjunction with a charged particle cancer therapy system
US8089054B2 (en) 2008-05-22 2012-01-03 Vladimir Balakin Charged particle beam acceleration and extraction method and apparatus used in conjunction with a charged particle cancer therapy system
US8093564B2 (en) 2008-05-22 2012-01-10 Vladimir Balakin Ion beam focusing lens method and apparatus used in conjunction with a charged particle cancer therapy system
US8129694B2 (en) 2008-05-22 2012-03-06 Vladimir Balakin Negative ion beam source vacuum method and apparatus used in conjunction with a charged particle cancer therapy system
US8129699B2 (en) 2008-05-22 2012-03-06 Vladimir Balakin Multi-field charged particle cancer therapy method and apparatus coordinated with patient respiration
US8144832B2 (en) 2008-05-22 2012-03-27 Vladimir Balakin X-ray tomography method and apparatus used in conjunction with a charged particle cancer therapy system
US8178859B2 (en) 2008-05-22 2012-05-15 Vladimir Balakin Proton beam positioning verification method and apparatus used in conjunction with a charged particle cancer therapy system
US10143854B2 (en) 2008-05-22 2018-12-04 Susan L. Michaud Dual rotation charged particle imaging / treatment apparatus and method of use thereof
US8188688B2 (en) 2008-05-22 2012-05-29 Vladimir Balakin Magnetic field control method and apparatus used in conjunction with a charged particle cancer therapy system
US8198607B2 (en) 2008-05-22 2012-06-12 Vladimir Balakin Tandem accelerator method and apparatus used in conjunction with a charged particle cancer therapy system
US10092776B2 (en) 2008-05-22 2018-10-09 Susan L. Michaud Integrated translation/rotation charged particle imaging/treatment apparatus and method of use thereof
US8288742B2 (en) 2008-05-22 2012-10-16 Vladimir Balakin Charged particle cancer therapy patient positioning method and apparatus
US8309941B2 (en) 2008-05-22 2012-11-13 Vladimir Balakin Charged particle cancer therapy and patient breath monitoring method and apparatus
US8368038B2 (en) 2008-05-22 2013-02-05 Vladimir Balakin Method and apparatus for intensity control of a charged particle beam extracted from a synchrotron
US8373145B2 (en) 2008-05-22 2013-02-12 Vladimir Balakin Charged particle cancer therapy system magnet control method and apparatus
US8373143B2 (en) 2008-05-22 2013-02-12 Vladimir Balakin Patient immobilization and repositioning method and apparatus used in conjunction with charged particle cancer therapy
US8374314B2 (en) 2008-05-22 2013-02-12 Vladimir Balakin Synchronized X-ray / breathing method and apparatus used in conjunction with a charged particle cancer therapy system
US8373146B2 (en) 2008-05-22 2013-02-12 Vladimir Balakin RF accelerator method and apparatus used in conjunction with a charged particle cancer therapy system
KR101233862B1 (en) * 2008-05-22 2013-02-15 블라디미르 예고르비치 발라킨 X―ray method and apparatus used in conjunction with a charged particle cancer therapy system
US8378321B2 (en) 2008-05-22 2013-02-19 Vladimir Balakin Charged particle cancer therapy and patient positioning method and apparatus
US8378311B2 (en) 2008-05-22 2013-02-19 Vladimir Balakin Synchrotron power cycling apparatus and method of use thereof
US8384053B2 (en) 2008-05-22 2013-02-26 Vladimir Balakin Charged particle beam extraction method and apparatus used in conjunction with a charged particle cancer therapy system
US8399866B2 (en) 2008-05-22 2013-03-19 Vladimir Balakin Charged particle extraction apparatus and method of use thereof
US8415643B2 (en) 2008-05-22 2013-04-09 Vladimir Balakin Charged particle beam acceleration and extraction method and apparatus used in conjunction with a charged particle cancer therapy system
US8421041B2 (en) 2008-05-22 2013-04-16 Vladimir Balakin Intensity control of a charged particle beam extracted from a synchrotron
US8436327B2 (en) 2008-05-22 2013-05-07 Vladimir Balakin Multi-field charged particle cancer therapy method and apparatus
US8519365B2 (en) 2008-05-22 2013-08-27 Vladimir Balakin Charged particle cancer therapy imaging method and apparatus
US8569717B2 (en) 2008-05-22 2013-10-29 Vladimir Balakin Intensity modulated three-dimensional radiation scanning method and apparatus
US8581215B2 (en) 2008-05-22 2013-11-12 Vladimir Balakin Charged particle cancer therapy patient positioning method and apparatus
US8598543B2 (en) 2008-05-22 2013-12-03 Vladimir Balakin Multi-axis/multi-field charged particle cancer therapy method and apparatus
US8614554B2 (en) 2008-05-22 2013-12-24 Vladimir Balakin Magnetic field control method and apparatus used in conjunction with a charged particle cancer therapy system
US8614429B2 (en) 2008-05-22 2013-12-24 Vladimir Balakin Multi-axis/multi-field charged particle cancer therapy method and apparatus
US8624528B2 (en) 2008-05-22 2014-01-07 Vladimir Balakin Method and apparatus coordinating synchrotron acceleration periods with patient respiration periods
US10070831B2 (en) 2008-05-22 2018-09-11 James P. Bennett Integrated cancer therapy—imaging apparatus and method of use thereof
US9168392B1 (en) 2008-05-22 2015-10-27 Vladimir Balakin Charged particle cancer therapy system X-ray apparatus and method of use thereof
US8637833B2 (en) 2008-05-22 2014-01-28 Vladimir Balakin Synchrotron power supply apparatus and method of use thereof
US8637818B2 (en) 2008-05-22 2014-01-28 Vladimir Balakin Magnetic field control method and apparatus used in conjunction with a charged particle cancer therapy system
US8642978B2 (en) 2008-05-22 2014-02-04 Vladimir Balakin Charged particle cancer therapy dose distribution method and apparatus
US8710462B2 (en) 2008-05-22 2014-04-29 Vladimir Balakin Charged particle cancer therapy beam path control method and apparatus
US8718231B2 (en) 2008-05-22 2014-05-06 Vladimir Balakin X-ray tomography method and apparatus used in conjunction with a charged particle cancer therapy system
US9981147B2 (en) 2008-05-22 2018-05-29 W. Davis Lee Ion beam extraction apparatus and method of use thereof
US8841866B2 (en) 2008-05-22 2014-09-23 Vladimir Yegorovich Balakin Charged particle beam extraction method and apparatus used in conjunction with a charged particle cancer therapy system
US8896239B2 (en) 2008-05-22 2014-11-25 Vladimir Yegorovich Balakin Charged particle beam injection method and apparatus used in conjunction with a charged particle cancer therapy system
US8901509B2 (en) 2008-05-22 2014-12-02 Vladimir Yegorovich Balakin Multi-axis charged particle cancer therapy method and apparatus
US9974978B2 (en) 2008-05-22 2018-05-22 W. Davis Lee Scintillation array apparatus and method of use thereof
US9937362B2 (en) 2008-05-22 2018-04-10 W. Davis Lee Dynamic energy control of a charged particle imaging/treatment apparatus and method of use thereof
US9155911B1 (en) 2008-05-22 2015-10-13 Vladimir Balakin Ion source method and apparatus used in conjunction with a charged particle cancer therapy system
US8957396B2 (en) 2008-05-22 2015-02-17 Vladimir Yegorovich Balakin Charged particle cancer therapy beam path control method and apparatus
US9910166B2 (en) 2008-05-22 2018-03-06 Stephen L. Spotts Redundant charged particle state determination apparatus and method of use thereof
US8969834B2 (en) 2008-05-22 2015-03-03 Vladimir Balakin Charged particle therapy patient constraint apparatus and method of use thereof
US8975600B2 (en) 2008-05-22 2015-03-10 Vladimir Balakin Treatment delivery control system and method of operation thereof
US9018601B2 (en) 2008-05-22 2015-04-28 Vladimir Balakin Multi-field charged particle cancer therapy method and apparatus coordinated with patient respiration
WO2009142548A2 (en) * 2008-05-22 2009-11-26 Vladimir Yegorovich Balakin X-ray method and apparatus used in conjunction with a charged particle cancer therapy system
US9058910B2 (en) 2008-05-22 2015-06-16 Vladimir Yegorovich Balakin Charged particle beam acceleration method and apparatus as part of a charged particle cancer therapy system
US9056199B2 (en) 2008-05-22 2015-06-16 Vladimir Balakin Charged particle treatment, rapid patient positioning apparatus and method of use thereof
US9044600B2 (en) 2008-05-22 2015-06-02 Vladimir Balakin Proton tomography apparatus and method of operation therefor
US9855444B2 (en) 2008-05-22 2018-01-02 Scott Penfold X-ray detector for proton transit detection apparatus and method of use thereof
US10029122B2 (en) 2008-05-22 2018-07-24 Susan L. Michaud Charged particle—patient motion control system apparatus and method of use thereof
US9177751B2 (en) 2008-05-22 2015-11-03 Vladimir Balakin Carbon ion beam injector apparatus and method of use thereof
US9782140B2 (en) 2008-05-22 2017-10-10 Susan L. Michaud Hybrid charged particle / X-ray-imaging / treatment apparatus and method of use thereof
US9314649B2 (en) 2008-05-22 2016-04-19 Vladimir Balakin Fast magnet method and apparatus used in conjunction with a charged particle cancer therapy system
US9757594B2 (en) 2008-05-22 2017-09-12 Vladimir Balakin Rotatable targeting magnet apparatus and method of use thereof in conjunction with a charged particle cancer therapy system
US9744380B2 (en) 2008-05-22 2017-08-29 Susan L. Michaud Patient specific beam control assembly of a cancer therapy apparatus and method of use thereof
US9498649B2 (en) 2008-05-22 2016-11-22 Vladimir Balakin Charged particle cancer therapy patient constraint apparatus and method of use thereof
US9737733B2 (en) 2008-05-22 2017-08-22 W. Davis Lee Charged particle state determination apparatus and method of use thereof
US9543106B2 (en) 2008-05-22 2017-01-10 Vladimir Balakin Tandem charged particle accelerator including carbon ion beam injector and carbon stripping foil
US9579525B2 (en) 2008-05-22 2017-02-28 Vladimir Balakin Multi-axis charged particle cancer therapy method and apparatus
US9616252B2 (en) 2008-05-22 2017-04-11 Vladimir Balakin Multi-field cancer therapy apparatus and method of use thereof
US9682254B2 (en) 2008-05-22 2017-06-20 Vladimir Balakin Cancer surface searing apparatus and method of use thereof
US9737734B2 (en) 2008-05-22 2017-08-22 Susan L. Michaud Charged particle translation slide control apparatus and method of use thereof
US9737272B2 (en) 2008-05-22 2017-08-22 W. Davis Lee Charged particle cancer therapy beam state determination apparatus and method of use thereof
US8229072B2 (en) 2008-07-14 2012-07-24 Vladimir Balakin Elongated lifetime X-ray method and apparatus used in conjunction with a charged particle cancer therapy system
US8625739B2 (en) 2008-07-14 2014-01-07 Vladimir Balakin Charged particle cancer therapy x-ray method and apparatus
US8627822B2 (en) 2008-07-14 2014-01-14 Vladimir Balakin Semi-vertical positioning method and apparatus used in conjunction with a charged particle cancer therapy system
WO2010058330A1 (en) * 2008-11-21 2010-05-27 Philips Intellectual Property & Standards Gmbh X-ray tube with switchable grid for gating of electron beam current during voltage breakdown
US8791435B2 (en) 2009-03-04 2014-07-29 Vladimir Egorovich Balakin Multi-field charged particle cancer therapy method and apparatus
US8907309B2 (en) 2009-04-17 2014-12-09 Stephen L. Spotts Treatment delivery control system and method of operation thereof
WO2011018729A1 (en) * 2009-08-13 2011-02-17 Koninklijke Philips Electronics N.V. X-ray tube with independent x- and z- dynamic focal spot deflection
CN102473574A (en) * 2009-08-13 2012-05-23 皇家飞利浦电子股份有限公司 X-ray tube with independent x- and z- dynamic focal spot deflection
WO2011083416A1 (en) * 2010-01-08 2011-07-14 Koninklijke Philips Electronics N.V. X-ray tube with a combined x- and y- focal spot deflection method
US10555710B2 (en) 2010-04-16 2020-02-11 James P. Bennett Simultaneous multi-axes imaging apparatus and method of use thereof
US10625097B2 (en) 2010-04-16 2020-04-21 Jillian Reno Semi-automated cancer therapy treatment apparatus and method of use thereof
US10518109B2 (en) 2010-04-16 2019-12-31 Jillian Reno Transformable charged particle beam path cancer therapy apparatus and method of use thereof
US9737731B2 (en) 2010-04-16 2017-08-22 Vladimir Balakin Synchrotron energy control apparatus and method of use thereof
US10029124B2 (en) 2010-04-16 2018-07-24 W. Davis Lee Multiple beamline position isocenterless positively charged particle cancer therapy apparatus and method of use thereof
US10751551B2 (en) 2010-04-16 2020-08-25 James P. Bennett Integrated imaging-cancer treatment apparatus and method of use thereof
US10638988B2 (en) 2010-04-16 2020-05-05 Scott Penfold Simultaneous/single patient position X-ray and proton imaging apparatus and method of use thereof
US11648420B2 (en) 2010-04-16 2023-05-16 Vladimir Balakin Imaging assisted integrated tomography—cancer treatment apparatus and method of use thereof
US10086214B2 (en) 2010-04-16 2018-10-02 Vladimir Balakin Integrated tomography—cancer treatment apparatus and method of use thereof
US10376717B2 (en) 2010-04-16 2019-08-13 James P. Bennett Intervening object compensating automated radiation treatment plan development apparatus and method of use thereof
US10188877B2 (en) 2010-04-16 2019-01-29 W. Davis Lee Fiducial marker/cancer imaging and treatment apparatus and method of use thereof
US10357666B2 (en) 2010-04-16 2019-07-23 W. Davis Lee Fiducial marker / cancer imaging and treatment apparatus and method of use thereof
US10349906B2 (en) 2010-04-16 2019-07-16 James P. Bennett Multiplexed proton tomography imaging apparatus and method of use thereof
US10179250B2 (en) 2010-04-16 2019-01-15 Nick Ruebel Auto-updated and implemented radiation treatment plan apparatus and method of use thereof
US10589128B2 (en) 2010-04-16 2020-03-17 Susan L. Michaud Treatment beam path verification in a cancer therapy apparatus and method of use thereof
US10556126B2 (en) 2010-04-16 2020-02-11 Mark R. Amato Automated radiation treatment plan development apparatus and method of use thereof
US8963112B1 (en) 2011-05-25 2015-02-24 Vladimir Balakin Charged particle cancer therapy patient positioning method and apparatus
US8933651B2 (en) 2012-11-16 2015-01-13 Vladimir Balakin Charged particle accelerator magnet apparatus and method of use thereof
WO2016144897A1 (en) * 2013-10-29 2016-09-15 Varian Medical Systems, Inc. X-ray tube having magnetic quadrupoles for focusing and magnetic dipoles for steering
JP2016219432A (en) * 2013-10-29 2016-12-22 ヴァリアン メディカル システムズ インコーポレイテッド X-ray tube having planar emitter with tunable emission characteristics and performing magnetic steering and magnetic focusing
DE102014211694B4 (en) * 2014-06-18 2016-06-16 Siemens Healthcare Gmbh X-ray tube
DE102014211694A1 (en) * 2014-06-18 2015-12-24 Siemens Aktiengesellschaft X-ray tube
US10460899B2 (en) 2014-10-06 2019-10-29 Koninklijke Philips N.V. Modification arrangement for an X-ray generating device
US10008359B2 (en) 2015-03-09 2018-06-26 Varex Imaging Corporation X-ray tube having magnetic quadrupoles for focusing and magnetic dipoles for steering
CN107408481A (en) * 2015-03-09 2017-11-28 万睿视影像有限公司 X-ray tube with the magnetic quadrupole for focusing and the magnetic dipole for steering
CN107408481B (en) * 2015-03-09 2019-08-16 万睿视影像有限公司 X-ray tube with the magnetic quadrupole for focusing and the magnetic dipole for steering
US9907981B2 (en) 2016-03-07 2018-03-06 Susan L. Michaud Charged particle translation slide control apparatus and method of use thereof
US10037863B2 (en) 2016-05-27 2018-07-31 Mark R. Amato Continuous ion beam kinetic energy dissipater apparatus and method of use thereof
EP3396696A1 (en) * 2017-04-27 2018-10-31 Imatrex, Inc. Compact deflecting magnet
RU2693565C1 (en) * 2017-04-27 2019-07-03 Иматрекс, Инк. Compact deflecting magnet
EP3537469A1 (en) * 2017-04-27 2019-09-11 Imatrex, Inc. Compact deflecting magnet
CN108807119A (en) * 2017-04-27 2018-11-13 伊玛曲公司 Compact deflecting magnet
US20190259565A1 (en) * 2017-04-27 2019-08-22 Imatrex Inc. Compact deflecting magnet
US10332718B1 (en) 2017-04-27 2019-06-25 Imatrex, Inc. Compact deflecting magnet
JP2019149387A (en) * 2017-04-27 2019-09-05 アイマトレックス，インコーポレイテッド Compact deflecting magnet
CN108807119B (en) * 2017-04-27 2022-01-21 伊玛曲公司 Compact bias magnet
JP7022718B2 (en) 2017-04-27 2022-02-18 アイマトレックス，インコーポレイテッド Small deflection magnet
US10290463B2 (en) 2017-04-27 2019-05-14 Imatrex, Inc. Compact deflecting magnet
TWI820158B (en) * 2018-06-25 2023-11-01 瑞典商艾希凜有限公司 X-ray source for emitting x-ray radiation and method for generating x-ray radiation

Also Published As

Publication number Publication date
CN103177919A (en) 2013-06-26
EP2074642A2 (en) 2009-07-01
EP2074642B1 (en) 2011-01-19
WO2008044194A3 (en) 2008-06-12
ATE496389T1 (en) 2011-02-15
CN103177919B (en) 2016-12-28
DE602007012126D1 (en) 2011-03-03
CN101523544A (en) 2009-09-02
US20100020937A1 (en) 2010-01-28
US7839979B2 (en) 2010-11-23

Similar Documents

Publication Publication Date Title
EP2074642B1 (en) X-ray emitting device and method of producing an electron beam to produce x-ray radiation in an x-ray emitting device
US9991085B2 (en) Apparatuses and methods for generating distributed x-rays in a scanning manner
US9916961B2 (en) X-ray tube having magnetic quadrupoles for focusing and steering
EP2443643B1 (en) X-ray tube for generating two focal spots and medical device comprising same
EP2082412B1 (en) X-ray tube, x-ray system, and method for generating x-rays
JP2004528682A (en) X-ray tube whose focus is electrostatically controlled by two filaments
US10008359B2 (en) X-ray tube having magnetic quadrupoles for focusing and magnetic dipoles for steering
JPH07296751A (en) X-ray tube device
EP2465131B1 (en) X-ray tube with independent x- and z- dynamic focal spot deflection
WO2008155695A1 (en) Magnetic lens system for spot control in an x-ray tube
US20180211809A1 (en) Cathode head with multiple filaments for high emission focal spot
KR20180098569A (en) Electromagnetic induction and receiving elements
US8401143B2 (en) Arrangement for three-dimensional electron beam tomography
JP2019519900A (en) Cathode assembly for use in generating x-rays
JP2012234810A (en) X-ray tube and x-ray tube operating method
US10121629B2 (en) Angled flat emitter for high power cathode with electrostatic emission control
CN109119312B (en) Magnetic scanning type X-ray tube
US8284900B2 (en) Apparatus and method for improved transient response in an electromagnetically controlled X-ray tube
US10032595B2 (en) Robust electrode with septum rod for biased X-ray tube cathode
US10102999B2 (en) Asymmetric core quadrupole with concave pole tips
EP3226277A1 (en) Angled flat emitter for high power cathode with electrostatic emission control
CN208903967U (en) A kind of X-ray tube of magnetic scanning formula
US20230320686A1 (en) Systems and methods for computed tomography
JP2013093102A (en) X-ray tube device and x-ray ct device

Legal Events

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

Ref document number: 200780037971.1

Country of ref document: CN

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

Ref document number: 07826677

Country of ref document: EP

Kind code of ref document: A2

WWE Wipo information: entry into national phase

Ref document number: 2007826677

Country of ref document: EP

WWE Wipo information: entry into national phase

Ref document number: 12444745

Country of ref document: US

NENP Non-entry into the national phase

Ref country code: DE

WWE Wipo information: entry into national phase

Ref document number: 2569/CHENP/2009

Country of ref document: IN