EP1906432B1 - Korrektur von Bildfehlern einer Elektronstrahlbildverstärkerröhre - Google Patents

Korrektur von Bildfehlern einer Elektronstrahlbildverstärkerröhre Download PDF

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Publication number
EP1906432B1
EP1906432B1 EP07116775A EP07116775A EP1906432B1 EP 1906432 B1 EP1906432 B1 EP 1906432B1 EP 07116775 A EP07116775 A EP 07116775A EP 07116775 A EP07116775 A EP 07116775A EP 1906432 B1 EP1906432 B1 EP 1906432B1
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EP
European Patent Office
Prior art keywords
radiation
input screen
photocathode
tube according
primary
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Not-in-force
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EP07116775A
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English (en)
French (fr)
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EP1906432A1 (de
Inventor
Andréas Koch
Daniel Gally
Clément Vallois
Eric Marche
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Thales SA
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Thales SA
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    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J31/00—Cathode ray tubes; Electron beam tubes
    • H01J31/08—Cathode ray tubes; Electron beam tubes having a screen on or from which an image or pattern is formed, picked up, converted, or stored
    • H01J31/50—Image-conversion or image-amplification tubes, i.e. having optical, X-ray, or analogous input, and optical output
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J2231/00—Cathode ray tubes or electron beam tubes
    • H01J2231/50—Imaging and conversion tubes
    • H01J2231/50057—Imaging and conversion tubes characterised by form of output stage

Definitions

  • the invention relates to the distortion correction of an image intensifier electron tube.
  • An image intensifier electron tube includes an input screen for receiving said primary electromagnetic radiation and an output screen emitting radiation depending on the primary radiation.
  • Intensifiers are for example used in medical radiology.
  • the intensifier receives X-radiation that has passed through the body of a patient.
  • the intensifier transmits on its second screen a visible image according to the X-radiation received by the input screen.
  • the intensifier amplifies the intensity of the received image.
  • this amplification makes it possible to reduce the dose of X-radiation received by the patient.
  • the amplification is carried out in a conventional manner by converting the radiation received by the input screen into emitted electrons in a cavity where the vacuum prevails.
  • the electrons are then accelerated by means of electrodes and then converted by the output screen into a visible image.
  • the invention is not limited to medical radiology, it can be implemented in all types of intensifiers whatever the radiation received or emitted by the screens.
  • the invention is for example applicable to light image intensifiers as for example described in the document FR 2 866 714 A1 .
  • the use of electrons accelerated by electrodes makes the intensifier sensitive to electromagnetic disturbances occurring in the environment of the intensifier. These disturbances create a spatial distortion of the image emitted by the output screen relative to the image received by the input screen.
  • Another solution is to project on the input screen a luminous pattern which we just analyze the distribution on the output screen as for example described in the documents WO 02/095457 - A2 and EP 0 949 651 A1 .
  • This solution avoids the displacement of mechanical parts such as the grid but is nevertheless cumbersome to implement and requires to interrupt the projection of the pattern to achieve a so-called useful image.
  • it is difficult to ensure sufficient dimensional stability of this pattern. In a common case, it would be necessary to ensure a stability of the order of 10 microns so that the accuracy of the test pattern is better than the dimension of a pixel in case of digitization of the image obtained on the output screen.
  • the invention aims to overcome the problems mentioned above by providing an intensifier tube in which the pattern can be permanently present without disturbing the primary radiation.
  • the subject of the invention is an image intensifier electronic tube according to claim 1.
  • the spectrum change of the primary radiation is common in medical imaging. For example, when using an X-ray source having a tube in which an electron beam is bombarding a target, a voltage change applied to electrodes accelerating the electron beam causes a change in the X-ray spectrum. Another reason for modifying the X-ray spectrum is related to the object whose image is to be obtained. Specifically, the thickness of an object (a patient in medical imaging) influences the spectrum of primary radiation received by the input screen.
  • An alteration of the primary radiation is generally not independent of the primary radiation spectrum and requires recalibration of the tube. The fact of not altering the primary radiation therefore avoids any recalibration between two successive images.
  • the figure 1 represents a tube 1 substantially elongated along an axis 2.
  • the tube 1 comprises a casing 3 inside which there is a sufficient vacuum so that electrons can move there.
  • An input screen 4 forms a first end of the envelope 3 and an exit screen 5 forms a second end of the envelope 3.
  • An input window 6 makes it possible to seal the envelope 3 at level of its first end. It is possible to dispense with the input window 6 and, in this case, the first screen 4 seals the envelope at its first end.
  • the output screen 5 can seal the envelope 3 at its second end.
  • X-radiation enters the tube 1 substantially along the axis 2 in a direction shown by an arrow 8.
  • This radiation through an object 9 which is to obtain a radiographic image.
  • the primary radiation for example X
  • the input screen 4 comprises a scintillator 10 on the face of the input screen 4 receiving X-radiation and a photocathode 11 on the opposite side of the input screen 4.
  • the scintillator 10 converts the primary radiation received by the input screen 4 into a secondary radiation such as for example visible light.
  • This secondary radiation is then absorbed by the photocathode 11 which converts it into electrons.
  • the electrons are then emitted inside the envelope 3 in the direction of the output screen 5.
  • the schematic path of the electrons inside the envelope 3 is materialized on the figure 1 by arrows 12.
  • the tube 1 also comprises several electrodes 13, 14, as well as an anode 15 located inside the envelope 3 making it possible to accelerate the electrons emitted by the photocathode 11 and guide them towards the output screen 5.
  • the acceleration of the electrons brings them energy allowing the intensification of the image.
  • the output screen 5 receives the electrons emitted by the photocathode 11 and converts them into radiation, for example visible, emitted towards the outside of the envelope 3 in the direction of the arrow 16.
  • This visible radiation may, for example , to be analyzed by a camera, represented on the figure 1 by its entrance pupil 17.
  • the optical axis of the entrance pupil 17 is substantially coincident with an axis of the output screen, in this case the axis 2.
  • the figure 2 is a pattern 20 belonging to the input screen 4.
  • the pattern 20 is formed of a plurality of points 21 distributed on the input screen 4.
  • the points 21 form for example a network uniformly distributed on the surface of the input screen 4.
  • the points 21 are for example round as shown on the figure 2 .
  • Other forms of points are of course possible, for example a square shape.
  • the target 20 comprises means for locally altering the secondary radiation which, for example, linearly modifies the transfer function between the primary radiation and the secondary radiation. In other words, at each point 21 of the target 20, the gain between the secondary radiation and the primary radiation is increased or decreased. The modification of the gain is determined so that the points 21 appear with sufficient contrast on the image obtained on the secondary screen 5 in the presence of an object 9 and at different doses of X-radiation.
  • figure 2 an example of evolution of the gain along an x axis crossing a point 21 in the form of a curve is shown. Outside point 21, the gain is maximum and inside the gain is reduced. Tests have shown that a reduction in gain of between 30 and 50% allows a certain recognition of the points 21 in the middle of an image of an object 9.
  • the tube comprises means making it possible to produce a light offset of the photocathode 11.
  • the corpuscular noise of this radiation can be important and make the recognition of the points difficult if the noise ratio on a signal is in the same order as the reduction of the gain by the points 21.
  • a remedy is the application of a luminous offset ie of a uniform illuminance of the photocathode 11.
  • this illumination is applied by a face of the input screen opposite to that which receives the primary radiation called the rear face of the input screen 4.
  • This light offset makes it possible to better detect the points 21.
  • the offset is then subtracted from the images obtained 5.
  • the offset also has an inherent corpuscular noise but is significantly lower than the corpuscular noise of the primary radiation. Of course, the offset noise must not exceed the primary radiation signal.
  • the offset is for example applied by means of a beam emitted by a light-emitting diode illuminating uniformly the rear face of the input screen 4.
  • the array of points 21 is moved under the influence of the magnetic fields in a non-homogeneous manner.
  • an example of a pattern 20 is shown on the figure 1 above the input screen 4.
  • An image 22 of this pattern 20, obtained on the output screen 5, is represented in continuous lines above the output screen 5.
  • an undistorted image of the pattern 20 on the output screen 5 has been shown in broken lines in superposition of the image 22.
  • the tube 1 comprises means for analyzing the distribution of the plurality of points 21 received by the output screen 5. More precisely, the measurement of this distortion is carried out by analyzing the distribution of the points in the image 22 of the target 20. For the points of the image located between the points of the target 20, the determination of the distortion can be done by interpolation from the measured distortion for the points of the target 20 closest to the considered point of the image 22.
  • the measurement can be absolute and the analysis consists in comparing the distribution of the points in the image 22 relative to to a theoretical distribution.
  • the measurement can be relative, and in this case, the comparison is made with respect to an image 22 made during a calibration phase during which the distortion of the image is controlled.
  • the means for locally altering the secondary radiation linearly modifies the transfer function between the primary radiation and the secondary radiation.
  • the transfer function is determined so as not to completely mask the primary radiation at the points 21 to be able to reconstruct the information contained in the primary radiation with the aid of a suitable treatment. More precisely, it has been realized that, in the absence of a pattern 20, the input screen 4 and more precisely the conversion between primary and secondary radiation has essentially multiplicative gain faults.
  • the defects already linearly alter the transfer function between the primary radiation and the secondary radiation. It is known to correct such defects for example by dividing a so-called useful image, obtained when X radiation passes through an object 9, by a reference image obtained when the same X radiation passes through no object.
  • the set of means for realizing the pattern belongs to the input screen 4 and more precisely, for each point 21 of the target 20, the means for locally altering the secondary radiation include a layer deposited on a surface of the input screen 4. This layer can be absorbent or reflective secondary radiation. It is indeed possible to increase the gain at point 21 instead of reducing it as explained in the box insert. figure 2 .
  • the figure 3 illustrates the operation of the points 21 of the target 20.
  • the input screen 4 formed by the scintillator 10 and the photocathode 11 and the input window 6.
  • the path of the primary radiation is materialized the arrows 8.
  • the primary radiation passes through the input screen 6 and is converted into secondary radiation whose path is represented by the arrows 30 which end on the photocathode 11 which transforms the secondary radiation into a beam of electrons 31.
  • the points 21 of the test pattern 20 are deposited and absorb a portion of the secondary radiation.
  • the absorption is indicated by arrows 30 in fine lines after passing through the point 21 by the secondary radiation.
  • the Figures 4a, 4b and 4c represents several examples of arrangement of the points 21 of the test pattern 20 on an input screen 4.
  • the scintillator 10 comprises a substrate 35 and a scintillator substance 36 for example made of cesium iodide.
  • the layer forming each point 21 is deposited on the substrate 35 and more precisely on one side of the substrate 35 carrying the scintillating substance 36.
  • the emission of the secondary radiation in the scintillating substance 36 is partly towards the rear, that is to say in a direction opposite to that of the arrow 8.
  • the layer forming each point 21 can either reflect the part of the secondary radiation emitted by the rear and in this case, the gain in the conversion between primary and secondary radiation is increased or absorb this part of the secondary radiation and in this case reduce the reflection of the secondary radiation on the substrate 35 and thus reduce the gain of the conversion.
  • the layer forming each point 21 is deposited on the intermediate layer 32 separating the scintillator 10 and the photocathode 11 is on the side of the scintillator 10, the case of the figure 4b , from side of the photocathode 11, case of the figure 4c .
  • the pattern can be made between the scintillator 10 and the intermediate layer 32 or between the intermediate layer 32 and the photocathode 11.
  • the intermediate layer 32 may comprise a conductive layer supplying the photocathode 11.
  • the pattern 20 may be made inside this conductive layer. In this case, it is advantageous to provide one or more additional layers to avoid degradation of the photocathode 11 and / or the conductive layer by the material of the pattern 20.
  • the layer may be made by vacuum evaporation of aluminum particles tending to reflect the second radiation, or carbon particles tending to absorb the second radiation.
  • the points 21 of the test pattern 20 are possible such as a local change of physical property of the surface of the scintillator 10 in contact with the intermediate layer 32.
  • a scintillating substance 36 such as cesium iodide is deposited on its substrate 35 in the form of needle growth.
  • the needle tips may be locally smoothed to locally alter the secondary radiation.
  • Another embodiment consists in making a physical or chemical modification of one of the components of the input screen 4. By way of example, it is possible to deviate from a stoichiometric composition or to modify crystalline properties.
  • the points 21 of the pattern 20 are made between the intermediate layer 32 and the photocathode 11, the points can alter the secondary radiation.
  • the points 21 then modify the gain of the photocathode 11 in the transformation of the energy carried by the secondary radiation into electron emission.
  • the photocathode 11 comprises for example a semiconductor material whose composition is stoichiometric. To achieve the points 21, one can for example deviate locally from the stoichiometric composition.
  • the modification of the gain of the photocathode 11 can also be implemented in a light image intensifier whose input screen is represented schematically on the figure 4e which is not part of the present invention.
  • This input screen has no scintillator and directly transforms the primary radiation into electrons. By acting on the gain of the photocathode 11, without altering the primary radiation, it is independent of the spectrum of the primary radiation.

Landscapes

  • Image-Pickup Tubes, Image-Amplification Tubes, And Storage Tubes (AREA)

Claims (12)

  1. Elektronische Bildverstärkerröhre, die einen Eingangsschirm (4) zum Empfangen von primärer elektromagnetischer Strahlung und einen Ausgangsschirm (5) umfasst, der in Abhängigkeit von der Primärstrahlung eine Strahlung emittiert, wobei der Eingangsschirm Folgendes umfasst:
    • eine Fotokathode (11), die einen Strahl von Elektroden in der Röhre in Richtung des Ausgangsschirms (5) emittiert, wobei die Emission des Elektronenstrahls von der Primärstrahlung abhängt,
    • einen Szintillator (10), der in Richtung der Bahn der Primärstrahlung vor der Fotokathode positioniert ist und die Primärstrahlung in sekundäre elektromagnetische Strahlung (30) umwandelt, für die die Fotokathode (11) empfindlich ist, wobei der von der Fotokathode (11) emittierte Elektronenstrahl von der Sekundärstrahlung (30) abhängt (30),
    dadurch gekennzeichnet, dass der Eingangsschirm (4) ferner ein Visier (20) umfasst, das in Richtung der Bahn der Primärstrahlung vor der Fotokathode platziert ist und von mehreren Punkten (21) gebildet wird, die auf dem Eingangsschirm (4) verteilt sind, und dadurch, dass die Punkte (21) die Sekundärstrahlung (30) örtlich verändern, ohne die Primärstrahlung zu verändern.
  2. Röhre nach Anspruch 1, dadurch gekennzeichnet, dass das Visier (20) permanent auf dem Eingangsschirm (4) vorhanden ist.
  3. Röhre nach einem der vorherigen Ansprüche, dadurch gekennzeichnet, dass die Punkte (21) die Transferfunktion zwischen der Primärstrahlung und der Sekundärstrahlung linear modifizieren.
  4. Röhre nach einem der vorherigen Ansprüche, dadurch gekennzeichnet, dass die Punkte (21) für die Sekundärstrahlung teiltransparent sind.
  5. Röhre nach einem der vorherigen Ansprüche, dadurch gekennzeichnet, dass jeder Punkt (21) des Visiers (20) eine Schicht auf einer Oberfläche (32, 35) des Eingangsschirms (4) aufweist.
  6. Röhre nach Anspruch 5, dadurch gekennzeichnet, dass die Schicht die Sekundärstrahlung absorbiert.
  7. Röhre nach Anspruch 5, dadurch gekennzeichnet, dass die Schicht die Sekundärstrahlung reflektiert.
  8. Röhre nach einem der Ansprüche 5 bis 7, dadurch gekennzeichnet, dass der Szintillator (10) ein Substrat (10) und eine auf dem Substrat (35) liegende Szintillationssubstanz (36) umfasst, und dadurch, dass die Schicht auf dem Substrat (35) angeordnet ist.
  9. Röhre nach einem der Ansprüche 5 bis 7, dadurch gekennzeichnet, dass die Schicht zwischen dem Szintillator (10) und der Fotokathode (11) angeordnet ist.
  10. Röhre nach einem der vorherigen Ansprüche, dadurch gekennzeichnet, dass sie Mittel zum Analysieren der Verteilung der von dem Ausgangsschirm (5) empfangenen mehreren Punkte (21) auf dem Visier umfasst.
  11. Röhre nach einem der vorherigen Ansprüche, dadurch gekennzeichnet, dass sie Mittel zum Erzeugen eines Lichtversatzes der Fotokathode (11) umfasst.
  12. Röhre nach einem der vorherigen Ansprüche, dadurch gekennzeichnet, dass alle Mittel zum Erzeugen des Visiers (20) zum Eingangsschirm (4) gehören.
EP07116775A 2006-09-26 2007-09-19 Korrektur von Bildfehlern einer Elektronstrahlbildverstärkerröhre Not-in-force EP1906432B1 (de)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
FR0608456A FR2906400B1 (fr) 2006-09-26 2006-09-26 Correction de distorsion d'un tube electronique intensificateur d'image.

Publications (2)

Publication Number Publication Date
EP1906432A1 EP1906432A1 (de) 2008-04-02
EP1906432B1 true EP1906432B1 (de) 2011-04-27

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US (1) US7728519B2 (de)
EP (1) EP1906432B1 (de)
JP (1) JP2008084861A (de)
AT (1) ATE507575T1 (de)
DE (1) DE602007014157D1 (de)
FR (1) FR2906400B1 (de)

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2803394A1 (fr) * 1999-12-30 2001-07-06 Thomson Tubes Electroniques Systeme de detection d'image radiologique pour generateur de rayons x a balayage
FR2866714A1 (fr) * 2004-02-19 2005-08-26 Jean Claude Robin Procede et dispositif pour la capture d'images a grande dynamique de niveau d'eclairement

Family Cites Families (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4474061A (en) 1981-11-27 1984-10-02 Motorola, Inc. Sonic pressure volume measuring device
FR2687007B1 (fr) * 1992-01-31 1994-03-25 Thomson Tubes Electroniques Tube intensificateur d'image notamment du type a focalisation de proximite.
JP3842353B2 (ja) * 1996-11-27 2006-11-08 浜松ホトニクス株式会社 Ｘ線イメージインテンシファイアの軸ずれ補正装置及びそれを備えたプリント基板穴開け装置
FR2777112B1 (fr) * 1998-04-07 2000-06-16 Thomson Tubes Electroniques Dispositif de conversion d'une image
FR2824922B1 (fr) * 2001-05-18 2004-10-29 Thales Sa Correction de distorsion d'un intensificateur d'image
WO2002095457A2 (en) 2001-05-22 2002-11-28 Bookham Technology Plc Method of defining grating patterns for optical waveguide devices
US7557503B2 (en) * 2004-09-22 2009-07-07 Hamamatsu Photonics K.K. Streak tube including control electrode having blocking portion between a photocathode and an anode

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2803394A1 (fr) * 1999-12-30 2001-07-06 Thomson Tubes Electroniques Systeme de detection d'image radiologique pour generateur de rayons x a balayage
FR2866714A1 (fr) * 2004-02-19 2005-08-26 Jean Claude Robin Procede et dispositif pour la capture d'images a grande dynamique de niveau d'eclairement

Also Published As

Publication number Publication date
JP2008084861A (ja) 2008-04-10
FR2906400A1 (fr) 2008-03-28
FR2906400B1 (fr) 2008-11-14
EP1906432A1 (de) 2008-04-02
US20080073492A1 (en) 2008-03-27
DE602007014157D1 (de) 2011-06-09
US7728519B2 (en) 2010-06-01
ATE507575T1 (de) 2011-05-15

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