EP0312850A1 - X-ray diagnostic apparatus - Google Patents
X-ray diagnostic apparatus Download PDFInfo
- Publication number
- EP0312850A1 EP0312850A1 EP88116591A EP88116591A EP0312850A1 EP 0312850 A1 EP0312850 A1 EP 0312850A1 EP 88116591 A EP88116591 A EP 88116591A EP 88116591 A EP88116591 A EP 88116591A EP 0312850 A1 EP0312850 A1 EP 0312850A1
- Authority
- EP
- European Patent Office
- Prior art keywords
- detector
- semiconductor detector
- ray
- image intensifier
- image
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
Images
Classifications
-
- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
- H05G—X-RAY TECHNIQUE
- H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor
- H05G1/08—Electrical details
- H05G1/64—Circuit arrangements for X-ray apparatus incorporating image intensifiers
-
- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
- H05G—X-RAY TECHNIQUE
- H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor
- H05G1/08—Electrical details
- H05G1/26—Measuring, controlling or protecting
- H05G1/30—Controlling
- H05G1/36—Temperature of anode; Brightness of image power
-
- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
- H05G—X-RAY TECHNIQUE
- H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor
- H05G1/08—Electrical details
- H05G1/26—Measuring, controlling or protecting
- H05G1/30—Controlling
- H05G1/38—Exposure time
- H05G1/42—Exposure time using arrangements for switching when a predetermined dose of radiation has been applied, e.g. in which the switching instant is determined by measuring the electrical energy supplied to the tube
- H05G1/44—Exposure time using arrangements for switching when a predetermined dose of radiation has been applied, e.g. in which the switching instant is determined by measuring the electrical energy supplied to the tube in which the switching instant is determined by measuring the amount of radiation directly
Definitions
- the invention relates to an X-ray diagnostic system with an image intensifier television chain and a detector for the average image brightness on the output fluorescent screen of the X-ray image intensifier in a predetermined range, in which the detector is a semiconductor detector with an area on which the entire output image of the X-ray image intensifier can be imaged, and at the means for selecting a predetermined area of the semiconductor detector for signal generation are present.
- An X-ray diagnostic system of this type is described in EP-A-0 217 456.
- An array of individual detectors is provided as the detector, which permits the formation of a brightness signal for a measuring field in the output image of the X-ray image intensifier.
- a downstream amplifier must be provided for each detector element, which means a considerable outlay in terms of circuitry.
- the invention is based on the object of designing an X-ray diagnostic system of the type mentioned at the outset in such a way that a lower circuit complexity than that of the prior art is provided for forming a large number of measuring fields with a variable shape.
- the detector is a large-area semiconductor detector, in front of which there is an aperture made of a liquid crystal matrix, which can be controlled by a control device for selecting a predetermined area on the semiconductor detector that is hit by the light.
- This solution results in a particularly low outlay for signal processing.
- the measuring field is selected electronically using the liquid crystal matrix.
- the formation of the measurement signal is not like that of a matrix photosensitive elements a variety of amplifiers, but only a single amplifier required.
- FIG. 1 shows an X-ray tube 1, which is fed by an X-ray generator 2.
- a patient 3 is irradiated by the X-rays.
- the x-ray image is amplified by an x-ray image intensifier 4.
- the amplified x-ray image appearing on the output screen of the x-ray image intensifier 4 is recorded by a television camera 5 and displayed on a display unit 7 via a television center 6.
- a semiconductor detector 8 is provided as an actual value transmitter, which feeds a corresponding signal to the actual value input of a comparator 9 via a measuring transducer 10.
- the comparator 9 has a setpoint input 11, at which there is a signal corresponding to the setpoint of the average image brightness in the measuring field of the output screen of the X-ray image intensifier 4.
- the x-ray generator 2 is influenced by a brightness control device 13 in the sense of an adjustment of the actual value to the target value.
- a setpoint generator 12 is provided for setting the setpoint.
- the semiconductor detector 8 has an area on which the entire output image of the X-ray image intensifier 4 can be reproduced, with the aid of a partially transparent mirror 14 in the beam path between the exit fluorescent screen of the X-ray image intensifier 4 and the television camera 5.
- a control device 15 selects electronically a predetermined area of the semiconductor detector 8 corresponding to the desired measuring field.
- the semiconductor detector 8 allows the selection of a large number of measuring fields, both with regard to their position and their shape and size.
- Fig. 2 shows an embodiment of a semiconductor detector 8 as a large-area detector, which is composed of a single detector element, e.g. is formed by a single photodiode.
- a semiconductor detector 8 is composed of a single detector element, e.g. is formed by a single photodiode.
- an aperture made of a liquid crystal matrix with liquid crystals 17 is arranged in the beam path in front of the semiconductor detector 8.
- the light transmission of the individual liquid crystals 17 can be controlled by the control device 15 to select a predetermined area hit by the light on the semiconductor detector 8. 2 shows, for example, the choice of three measuring fields, a central measuring field and two lateral measuring fields.
- signal evaluation within the measurement field is also possible.
- the measuring signal of each individual photodiode of the measuring field matrix is electronically multiplied by a weighting factor before being added to the total actual value signal.
- the weighting factors can be selected on an X-ray system with organ operation depending on the object.
- a corresponding evaluation is possible in the detector embodiment according to FIG. 2, in that not all liquid crystals 17 of the liquid crystal matrix within the measuring surface are controlled for light transmission. By varying the liquid crystals controlled for permeability per unit area in the area of the measuring field, an adaptation to the object to be examined is possible.
- peak value regulation can also take place, in that the signals of the individual matrix elements of the selected measuring field are read out serially and only the maximum value of the determined signal distribution is used for the actual value formation becomes.
- methods of pattern recognition can also be used when selecting the matrix elements that contribute to the actual value signal formation.
- the technique of measuring field formation shown here for a television camera can also be used in the indirect technique with a sheet film camera.
- the semiconductor detector is also used for direct recording instead of an ionization chamber, the advantages mentioned (flexible measurement field formation, signal evaluation, mean value / peak value control) can also be used here.
- exposure corrections are necessary for all hardening effects which occur when the radiation passes through the cassette, e.g. can be stored in tabular form in the memory of the exposure machine. If the patient transparency is determined by a previous fluoroscopy before the direct exposure is triggered and the selected display is also reported by the device to the automatic exposure device, the appropriate exposure correction can be found in the table.
Abstract
Description
Die Erfindung betrifft eine Röntgendiagnostikanlage mit einer Bildverstärker-Fernsehkette und einem Detektor für die mittlere Bildhelligkeit auf dem Ausgangsleuchtschirm des Röntgenbildverstärkers in einem vorbestimmten Bereich, bei der der Detektor ein Halbleiterdetektor mit einer Fläche ist, auf der das ganze Ausgangsbild des Röntgenbildverstärkers abbildbar ist, und bei der Mittel zur Auswahl eines vorbestimmten Bereiches des Halbleiterdetektors für die Signalerzeugung vorhanden sind.The invention relates to an X-ray diagnostic system with an image intensifier television chain and a detector for the average image brightness on the output fluorescent screen of the X-ray image intensifier in a predetermined range, in which the detector is a semiconductor detector with an area on which the entire output image of the X-ray image intensifier can be imaged, and at the means for selecting a predetermined area of the semiconductor detector for signal generation are present.
Eine Röntgendiagnostikanlage dieser Art ist in der EP-A-0 217 456 beschrieben. Als Detektor ist dabei ein Array aus Einzeldetektoren vorgesehen, das die Bildung eines Helligkeitssignals für ein Meßfeld im Ausgangsbild des Röntgenbildverstärkers erlaubt. Dabei muß für jedes Detektorelement ein nachgeschalteter Verstärker vorgesehen werden, was einen erheblichen schaltungstechnischen Aufwand bedeutet.An X-ray diagnostic system of this type is described in EP-A-0 217 456. An array of individual detectors is provided as the detector, which permits the formation of a brightness signal for a measuring field in the output image of the X-ray image intensifier. A downstream amplifier must be provided for each detector element, which means a considerable outlay in terms of circuitry.
Der Erfindung liegt die Aufgabe zugrunde, eine Röntgendiagnostikanlage der eingangs genannten Art so auszubilden, daß zur Bildung einer Vielzahl von Meßfeldern mit variabler Form ein gegenüber dem Stand der Technik geringerer schaltungstechnischer Aufwand vorgesehen ist.The invention is based on the object of designing an X-ray diagnostic system of the type mentioned at the outset in such a way that a lower circuit complexity than that of the prior art is provided for forming a large number of measuring fields with a variable shape.
Diese Aufgabe ist erfindungsgemäß dadurch gelöst, daß der Detektor ein großflächiger Halbleiterdetektor ist, vor dem eine Blende aus einer Flüssigkristall-Matrix liegt, die durch eine Steuervorrichtung zur Auswahl eines vorbestimmten, vom Licht getroffenen Bereiches auf dem Halbleiterdetektor ansteuerbar ist. Bei dieser Lösung ergibt sich ein besonders geringer Aufwand für die Signalaufbereitung. Die Meßfeldwahl erfolgt mit Hilfe der Flüssigkristall-Matrix in elektronischer Weise. Für die Bildung des Meßsignales ist nicht wie bei einer Matrix aus lichtempfindlichen Elementen eine Vielzahl von Verstärkern, sondern nur ein einziger Verstärker erforderlich.This object is achieved in that the detector is a large-area semiconductor detector, in front of which there is an aperture made of a liquid crystal matrix, which can be controlled by a control device for selecting a predetermined area on the semiconductor detector that is hit by the light. This solution results in a particularly low outlay for signal processing. The measuring field is selected electronically using the liquid crystal matrix. The formation of the measurement signal is not like that of a matrix photosensitive elements a variety of amplifiers, but only a single amplifier required.
Die Erfindung ist nachfolgend anhand eines in der Zeichnung dargestellten Ausführungsbeispiels näher erläutert. Es zeigen:
- Fig. 1 eine Röntgendiagnostikanlage nach der Erfindung, und
- Fig. 2 eine Ausführungsform für einen Detektor, der Röntgendiagnostikanlage gemäß Fig. 1.
- Fig. 1 is an X-ray diagnostic system according to the invention, and
- FIG. 2 shows an embodiment for a detector, the X-ray diagnostic system according to FIG. 1.
In der Fig. 1 ist eine Röntgenröhre 1 dargestellt, die von einem Röntgengenerator 2 gespeist wird. Ein Patient 3 wird von der Röntgenstrahlung durchstrahlt. Das Röntgenbild wird von einem Röntgenbildverstärker 4 verstärkt. Das am Ausgangsbildschirm des Röntgenbildverstärkers 4 erscheinende, verstärkte Röntgenbild wird von einer Fernsehkamera 5 aufgenommen und über eine Fernsehzentrale 6 auf einem Sichtgerät 7 wiedergegeben.1 shows an X-ray tube 1, which is fed by an X-ray generator 2. A patient 3 is irradiated by the X-rays. The x-ray image is amplified by an x-ray image intensifier 4. The amplified x-ray image appearing on the output screen of the x-ray image intensifier 4 is recorded by a television camera 5 and displayed on a display unit 7 via a television center 6.
Zur Konstanthaltung der mittleren Bildhelligkeit in einem Meßfeld des Ausgangsschirms des Röntgenbildverstärkers 4 ist ein Halbleiterdetektor 8 als Istwertgeber vorgesehen, der ein entsprechendes Signal dem Istwerteingang eines Vergleicher 9 über einen Meßwandler 10 zuführt. Der Vergleicher 9 weist einen Sollwerteingang 11 auf, an dem ein dem Sollwert der mittleren Bildhelligkeit im Meßfeld des Ausgangsschirms des Röngtgenbildverstärkers 4 entsprechendes Signal liegt. In Abhängigkeit von der Differenz zwischen Ist- und Sollwert wird der Röntgengenerator 2 von einer Helligkeitsregeleinrichtung 13 im Sinne eines Angleiches des Istwertes an den Sollwert beeinflußt. Für die Einstellung des Sollwertes ist ein Sollwertgeber 12 vorgesehen.In order to keep the mean image brightness constant in a measuring field of the output screen of the X-ray image intensifier 4, a
Der Halbleiterdetektor 8 hat eine Fläche, auf der das ganze Ausgangsbild des Röntgenbildverstärkers 4 abbildbar ist, und zwar mit Hilfe eines teildurchlässigen Spiegels 14 im Strahlengang zwischen dem Ausgangsleuchtschirm des Röntgenbildverstärkers 4 und der Fernsehkamera 5. Eine Steuervorrichtung 15 wählt dabei einen vorbestimmten Bereich des Halbleiterdetektors 8 entsprechend dem gewünschten Meßfeld elektronisch aus. Der Halbleiterdetektor 8 erlaubt dabei die Wahl einer Vielzahl von Meßfeldern, und zwar sowohl hinsichtlich ihrer Lage als auch ihrer Form und Größe.The
Die Fig. 2 zeigt eine Ausführungsform eines Halbleiterdetektors 8 als großflächigen Detektor, der von einem einzigen Detektorelement, also z.B. von einer einzigen Photodiode gebildet ist. Zur Auswahl des jeweils gewünschten Meßfeldes ist im Strahlengang vor dem Halbleiterdetektor 8 eine Blende aus einer Flüssigkristall-Matrix mit Flüssigkristallen 17 angeordnet. Die einzelnen Flüssigkristalle 17 können durch die Steuervorrichtung 15 zur Auswahl eines vorbestimmten, vom Licht getroffenen Bereiches auf dem Halbleiterdetektor 8 in ihrer Lichtdurchlässigkeit gesteuert werden. In Fig. 2 ist beispielsweise die Wahl dreier Meßfelder, eines zentralen Meßfeldes sowie zweier seitlicher Meßfelder dargestellt.Fig. 2 shows an embodiment of a
Bei der in Fig. 2 gezeigten Ausführungsform ist auch eine Signalbewertung innerhalb des Meßfeldes möglich. Dabei wird das Meßsignal jeder einzelnen Photodiode der Meßfeldmatrix vor der Addition zum Gesamtistwertsignal elektronisch mit einem Gewichtungsfaktor multipliziert. An einer Röntgenanlage mit Organbedienung kann die Wahl der Gewichtungsfaktoren objektabhängig erfolgen. Bei der Detektorausführung gemäß Fig. 2 ist eine entsprechende Bewertung möglich, indem nicht alle Flüssigkristalle 17 der Flüssigkristallmatrix innerhalb der Meßfläche auf Lichtdurchlässigkeit gesteuert werden. Durch eine Variation der auf Durchlässigkeit gesteuerten Flüssigkristalle pro Flächeneinheit im Bereich des Meßfeldes ist also eine Anpassung an das zu untersuchende Objekt möglich.In the embodiment shown in FIG. 2, signal evaluation within the measurement field is also possible. The measuring signal of each individual photodiode of the measuring field matrix is electronically multiplied by a weighting factor before being added to the total actual value signal. The weighting factors can be selected on an X-ray system with organ operation depending on the object. A corresponding evaluation is possible in the detector embodiment according to FIG. 2, in that not all
Weiterhin kann auch eine Spitzenwertregelung erfolgen, indem die Signale der einzelnen Matrixelemente des ausgewählten Meßfeldes seriell ausgelesen werden und nur der Maximalwert der ermittelten Signalverteilung zur Istwertbildung herangezogen wird. Für eine Anpassung der Regelung an unterschiedliche Objekte können bei der Auswahl der Matrixelemente, die zur Istwert-Signalbildung beitragen, auch Methoden der Mustererkennung angewendet werden.Furthermore, peak value regulation can also take place, in that the signals of the individual matrix elements of the selected measuring field are read out serially and only the maximum value of the determined signal distribution is used for the actual value formation becomes. To adapt the control to different objects, methods of pattern recognition can also be used when selecting the matrix elements that contribute to the actual value signal formation.
Die hier für eine Fernsehkamera dargestellte Technik der Meßfeldbildung ist auch anwendbar bei der Indirekt-Technik mit einer Blattfilmkamera.The technique of measuring field formation shown here for a television camera can also be used in the indirect technique with a sheet film camera.
Wird der Halbleiterdetektor anstelle einer Ionisationskammer auch für die Direktaufnahme verwendet, so können auch hier die angeführten Vorteile (flexible Meßfeldbildung, Signal-Bewertung, Mittelwert-/Spitzenwertregelung) genutzt werden. Nachdem der Bildverstärker hinter der Kassette angeordnet ist, sind für alle beim Durchgang der Strahlung durch die Kassette auftretenden Aufhärtungseffekte Belichtungskorrekturen erforderlich, die z.B. in tabellarischer Form im Speicher des Belichtungsautomaten abgelegt sein können. Wird vor Auslösung der Direktaufnahme die Patiententransparenz durch eine vorangehende Durchleuchtung ermittelt und wird außerdem die gewählte Einblendung vom Gerät an den Belichtungsautomaten gemeldet, kann die zutreffende Belichtungskorrektur der Tabelle entnommen werden.If the semiconductor detector is also used for direct recording instead of an ionization chamber, the advantages mentioned (flexible measurement field formation, signal evaluation, mean value / peak value control) can also be used here. After the image intensifier is arranged behind the cassette, exposure corrections are necessary for all hardening effects which occur when the radiation passes through the cassette, e.g. can be stored in tabular form in the memory of the exposure machine. If the patient transparency is determined by a previous fluoroscopy before the direct exposure is triggered and the selected display is also reported by the device to the automatic exposure device, the appropriate exposure correction can be found in the table.
Claims (1)
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE8714009U DE8714009U1 (en) | 1987-10-19 | 1987-10-19 | |
DE8714009U | 1987-10-19 |
Publications (2)
Publication Number | Publication Date |
---|---|
EP0312850A1 true EP0312850A1 (en) | 1989-04-26 |
EP0312850B1 EP0312850B1 (en) | 1992-08-12 |
Family
ID=6813240
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP88116591A Expired - Lifetime EP0312850B1 (en) | 1987-10-19 | 1988-10-06 | X-ray diagnostic apparatus |
Country Status (4)
Country | Link |
---|---|
US (1) | US5029338A (en) |
EP (1) | EP0312850B1 (en) |
JP (1) | JPH0163269U (en) |
DE (2) | DE8714009U1 (en) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR2803394A1 (en) * | 1999-12-30 | 2001-07-06 | Thomson Tubes Electroniques | X-RAY IMAGE DETECTION SYSTEM FOR SCANNING X-RAY GENERATOR |
Families Citing this family (17)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2548018Y2 (en) * | 1990-01-24 | 1997-09-17 | 興和 株式会社 | X-ray imaging device |
EP0480096B1 (en) * | 1990-10-12 | 1994-07-13 | Siemens Aktiengesellschaft | X-ray diagnostic apparatus comprising an X-ray image intensifier and a detector for its output screen image brightness |
DE4102445C1 (en) * | 1991-01-28 | 1992-03-05 | Siemens Ag, 8000 Muenchen, De | |
DE9107256U1 (en) * | 1991-06-12 | 1991-08-08 | Siemens Ag, 8000 Muenchen, De | |
US5311568A (en) * | 1992-05-01 | 1994-05-10 | Picker International, Inc. | Optical alignment means utilizing inverse projection of a test pattern/target |
DE4232901A1 (en) * | 1992-10-01 | 1994-04-07 | Siemens Ag | Medical X=Ray diagnostic equipment with optimum setting of emission control - has stray transmitted emission received by sensors to provide signal compared with reference to control generator |
US5651047A (en) * | 1993-01-25 | 1997-07-22 | Cardiac Mariners, Incorporated | Maneuverable and locateable catheters |
US5550378A (en) * | 1993-04-05 | 1996-08-27 | Cardiac Mariners, Incorporated | X-ray detector |
US5682412A (en) * | 1993-04-05 | 1997-10-28 | Cardiac Mariners, Incorporated | X-ray source |
WO1996020579A1 (en) * | 1994-12-23 | 1996-07-04 | Philips Electronics N.V. | X-ray examination apparatus comprising an exposure control circuit |
US5617462A (en) * | 1995-08-07 | 1997-04-01 | Oec Medical Systems, Inc. | Automatic X-ray exposure control system and method of use |
DE19842474A1 (en) * | 1998-09-16 | 2000-03-30 | Siemens Ag | Radiation detector for diagnostic X=ray device |
DE69913311T2 (en) * | 1998-10-19 | 2004-10-14 | Koninklijke Philips Electronics N.V. | X-RAY EXAMINATION DEVICE WITH REGULATION OF THE RADIATION DOSE |
US6275335B1 (en) | 1999-07-16 | 2001-08-14 | Sl3D, Inc. | Single-lens 3D method, microscope, and video adapter |
WO2001039558A1 (en) * | 1999-11-23 | 2001-05-31 | Koninklijke Philips Electronics N.V. | X-ray examination apparatus with exposure control |
US20020131170A1 (en) * | 2001-01-12 | 2002-09-19 | Bryan Costales | Stereoscopic aperture valves |
DE102004015326A1 (en) * | 2004-03-30 | 2005-10-20 | Leica Microsystems | Apparatus and method for inspecting a semiconductor device |
Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4185198A (en) * | 1976-07-08 | 1980-01-22 | Tokyo Shibaura Electric Co., Ltd. | Means for generating an X-ray exposure command in response to a video signal component |
EP0038666A1 (en) * | 1980-04-21 | 1981-10-28 | Technicare Corporation | Radiographic apparatus and method with automatic exposure control |
EP0200623A1 (en) * | 1985-04-19 | 1986-11-05 | Thomson-Cgr | Radiological apparatus |
FR2582502A1 (en) * | 1985-06-04 | 1986-12-05 | Thomson Cgr | Radiology installation with global compensator placed in an optical path of the image |
EP0217456A1 (en) * | 1985-09-20 | 1987-04-08 | Koninklijke Philips Electronics N.V. | An X-ray examination apparatus with a locally divided auxiliary detector |
Family Cites Families (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE2803913C2 (en) * | 1978-01-30 | 1986-01-30 | Siemens AG, 1000 Berlin und 8000 München | X-ray diagnostic system with an image intensifier television chain |
DE3141987A1 (en) * | 1981-10-22 | 1983-05-05 | Siemens AG, 1000 Berlin und 8000 München | X-RAY DIAGNOSTIC DEVICE |
NL8200852A (en) * | 1982-03-03 | 1983-10-03 | Philips Nv | ROENTGEN RESEARCH DEVICE. |
DE3225061A1 (en) * | 1982-07-05 | 1984-01-05 | Siemens AG, 1000 Berlin und 8000 München | X-RAY DIAGNOSTIC DEVICE |
FR2577374A1 (en) * | 1985-02-08 | 1986-08-14 | Thomson Cgr | Method of automatic adjustment of exposure in a radiology installation and radiology installation implementing such a method |
-
1987
- 1987-10-19 DE DE8714009U patent/DE8714009U1/de not_active Expired
-
1988
- 1988-09-15 US US07/244,343 patent/US5029338A/en not_active Expired - Fee Related
- 1988-10-06 EP EP88116591A patent/EP0312850B1/en not_active Expired - Lifetime
- 1988-10-06 DE DE8888116591T patent/DE3873680D1/en not_active Expired - Fee Related
- 1988-10-17 JP JP1988135401U patent/JPH0163269U/ja active Pending
Patent Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4185198A (en) * | 1976-07-08 | 1980-01-22 | Tokyo Shibaura Electric Co., Ltd. | Means for generating an X-ray exposure command in response to a video signal component |
EP0038666A1 (en) * | 1980-04-21 | 1981-10-28 | Technicare Corporation | Radiographic apparatus and method with automatic exposure control |
EP0200623A1 (en) * | 1985-04-19 | 1986-11-05 | Thomson-Cgr | Radiological apparatus |
FR2582502A1 (en) * | 1985-06-04 | 1986-12-05 | Thomson Cgr | Radiology installation with global compensator placed in an optical path of the image |
EP0217456A1 (en) * | 1985-09-20 | 1987-04-08 | Koninklijke Philips Electronics N.V. | An X-ray examination apparatus with a locally divided auxiliary detector |
Cited By (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR2803394A1 (en) * | 1999-12-30 | 2001-07-06 | Thomson Tubes Electroniques | X-RAY IMAGE DETECTION SYSTEM FOR SCANNING X-RAY GENERATOR |
WO2001050481A1 (en) * | 1999-12-30 | 2001-07-12 | Thales Electron Devices S.A. | Radiological image sensing system for scanning x-ray generator |
US6934360B2 (en) | 1999-12-30 | 2005-08-23 | Thales Electron Devices S.A. | Radiological image sensing system for a scanning x-ray generator |
US7082187B2 (en) | 1999-12-30 | 2006-07-25 | Thales Electron Devices S.A. | Radiological image detection system for a scanning X-ray generator |
Also Published As
Publication number | Publication date |
---|---|
DE8714009U1 (en) | 1989-02-16 |
DE3873680D1 (en) | 1992-09-17 |
JPH0163269U (en) | 1989-04-24 |
US5029338A (en) | 1991-07-02 |
EP0312850B1 (en) | 1992-08-12 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
EP0312850B1 (en) | X-ray diagnostic apparatus | |
DE3840736C2 (en) | ||
EP0234603B1 (en) | X-ray generator with control of dosing power | |
EP0362427B1 (en) | X-ray diagnostic apparatus with a detector for the average image brightness | |
DE2950767A1 (en) | X-RAY GENERATOR | |
EP0223432A2 (en) | X-ray radiography system | |
EP0480096B1 (en) | X-ray diagnostic apparatus comprising an X-ray image intensifier and a detector for its output screen image brightness | |
DE2851640A1 (en) | ELECTRON MICROSCOPE | |
DE19651722A1 (en) | Automatic exposure setting method for panorama or tomographic radiography device | |
DE3928282A1 (en) | X-RAY RECEIVING DEVICE | |
EP0106402B1 (en) | Method of producing tomographic images | |
DE2702009A1 (en) | RADIOGRAPHIC DEVICE | |
EP0471883B1 (en) | X-ray exposure automat | |
DE69815252T2 (en) | EXPOSURE CONTROL BASED ON A SIGNIFICANT PART OF AN X-RAY IMAGE | |
DE2803913C2 (en) | X-ray diagnostic system with an image intensifier television chain | |
DE2548531A1 (en) | Radio diagnostic technique with improved picture contrast - using beam splitting slit screens above and below object | |
DE1764414C3 (en) | X-ray slice imaging device with a drive means for generating a slice movement and with a television device | |
DE4102445C1 (en) | ||
DE19755764C2 (en) | Method for operating an X-ray diagnostic device with an X-ray image converter television chain and device for carrying out such a method | |
DE2207053A1 (en) | IMAGE ENHANCER DENSITOMETER | |
DE2141676A1 (en) | X-RAY IMAGE AMPLIFIER ARRANGEMENT | |
EP0121151B1 (en) | X-ray diagnostic apparatus | |
DE3433141C2 (en) | ||
DE4239957C2 (en) | X-ray imaging device | |
DE739973C (en) | Procedure for determining the most favorable recording voltage for X-ray recordings |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
PUAI | Public reference made under article 153(3) epc to a published international application that has entered the european phase |
Free format text: ORIGINAL CODE: 0009012 |
|
AK | Designated contracting states |
Kind code of ref document: A1 Designated state(s): DE FR GB |
|
17P | Request for examination filed |
Effective date: 19890529 |
|
17Q | First examination report despatched |
Effective date: 19920102 |
|
GRAA | (expected) grant |
Free format text: ORIGINAL CODE: 0009210 |
|
AK | Designated contracting states |
Kind code of ref document: B1 Designated state(s): DE FR GB |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: GB Payment date: 19920914 Year of fee payment: 5 |
|
REF | Corresponds to: |
Ref document number: 3873680 Country of ref document: DE Date of ref document: 19920917 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: FR Payment date: 19921016 Year of fee payment: 5 |
|
ET | Fr: translation filed | ||
GBT | Gb: translation of ep patent filed (gb section 77(6)(a)/1977) | ||
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: DE Payment date: 19921216 Year of fee payment: 5 |
|
PLBE | No opposition filed within time limit |
Free format text: ORIGINAL CODE: 0009261 |
|
STAA | Information on the status of an ep patent application or granted ep patent |
Free format text: STATUS: NO OPPOSITION FILED WITHIN TIME LIMIT |
|
26N | No opposition filed | ||
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: GB Effective date: 19931006 |
|
GBPC | Gb: european patent ceased through non-payment of renewal fee |
Effective date: 19931006 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: FR Effective date: 19940630 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: DE Effective date: 19940701 |
|
REG | Reference to a national code |
Ref country code: FR Ref legal event code: ST |