EP0151270B1 - X-ray diagnostic apparatus - Google Patents

X-ray diagnostic apparatus Download PDF

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Publication number
EP0151270B1
EP0151270B1 EP84115058A EP84115058A EP0151270B1 EP 0151270 B1 EP0151270 B1 EP 0151270B1 EP 84115058 A EP84115058 A EP 84115058A EP 84115058 A EP84115058 A EP 84115058A EP 0151270 B1 EP0151270 B1 EP 0151270B1
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EP
European Patent Office
Prior art keywords
signal
radiation detector
image
ray
integrator
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Expired
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EP84115058A
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German (de)
French (fr)
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EP0151270A1 (en
Inventor
Udo Heinze
Paul Marhoff
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Siemens AG
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Siemens AG
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    • 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
    • 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
    • H05G1/60—Circuit arrangements for obtaining a series of X-ray photographs or for X-ray cinematography

Definitions

  • the invention relates to an x-ray diagnostic system with a control circuit, which has a radiation detector for detecting the average dose in the dominant region and a control stage which influences at least one recording value as a function of the detector output signal.
  • An X-ray diagnostic system of this type in which the control circuit has an integrator for the signal of the radiation detector and the control stage switches off the high voltage on the X-ray tube when a predetermined dose per image is reached.
  • a control circuit of this type is called an exposure machine.
  • the automatic exposure device can have an image intensifier and a downstream photomultiplier as the radiation detector, which detects the average image brightness in the beam path between the exit fluorescent screen of the X-ray image intensifier and an image capturing device in a predetermined range.
  • incorrect exposures can occur if the contrast in the area detected by the radiation detector changes during the series.
  • the invention has for its object to provide an X-ray diagnostic system of the type mentioned in such a way that optimum image blackening or brightness is achieved even with a large change in contrast in the area detected by the radiation detector.
  • a tube-near second radiation detector is provided, which is followed by a memory for a signal dependent on the dose rate in the last image, that the memory signal is fed as a reference signal to a second control stage and that a changeover switch is present which the first control stage can be switched off and the second control stage can be switched on, to which a signal dependent on the current output signal of the second radiation detector can then be fed at a second input.
  • a switch is made to a second radiation detector located in front of the patient, which also delivers an output signal before the switchover.
  • an X-ray tube 1 is shown, which is fed by an X-ray generator 2 and shines through a patient 3.
  • the x-ray images are first generated on the input fluorescent screen of an x-ray image intensifier 4, the output image of which is recorded by a television camera 5 and displayed on a montior 6. Furthermore, the output image of the X-ray image intensifier 4 can be captured using a film camera 7.
  • a radiation detector 8 is provided, which detects the average image brightness in a predetermined range.
  • a semi-transparent mirror 9 is provided in the beam path between the exit fluorescent screen of the X-ray image intensifier 4 and the television camera 5.
  • Another semitransparent mirror 10 supplies the x-ray image to the film camera 7.
  • the output signal of the photomultiplier 8 is converted via a current-voltage converter 10 into a corresponding voltage, which is integrated in an integrator 11. Accordingly, there is a signal at the input 12 of a switching stage 13 which corresponds to the dose accumulated for an image.
  • a reference signal is applied to input 14 of switching stage 13. As soon as the signal at the input 12 reaches the signal at the input 14, the switching stage 13 switches off the X-ray tube voltage 1 via the switch 15, which initially assumes its fully drawn position.
  • the X-ray diagnostic system shown has a second, near-tube radiation detector 16, the output signal of which is converted via a current-voltage converter 17 into a corresponding voltage, which is integrated in an integrator 18.
  • the output signal of the integrator 18 is integrated in a memory 20 via a switch 19 which initially assumes its fully drawn position and is supplied as a reference voltage to a second switching stage 21.
  • the switch 15 separates the output of the switching stage 13 from the X-ray generator 2 and switches the output of the switching stage 21 on.
  • the switch 19 feeds the output signal of the integrator 18 to the switching stage 21 as an actual value signal.
  • the setpoint signal is the reference voltage that is supplied by the memory 20.
  • the memory 20 supplies a reference voltage which corresponds to the dose reached in the last picture before the switches 15, 19 were actuated. Before this actuation, it is reset after each image switched by the exposure machine 8 to 13. This also applies to the integrator 18.
  • the images are accordingly switched automatically with a dose which was achieved in the last image of a test series switched by the automatic exposure devices 8 to 13 and which accordingly leads to an optimal image blackening.
  • the arrival of a contrast medium in the examined area has no effect on the output signal of the radiation detector 16 and thus on the image blackening.
  • the automatic exposure device 16 to 21 it is achieved that, particularly when the automatic exposure device 8 to 13 is switched off, mains voltage fluctuations, changes in the X-ray tube current with unchanged setting value (reaction of the anode), beat phenomena with a cycle of the recording in which the X-ray tube 1 is not synchronized with the network is pulsed, and influences of transient processes of the X-ray tube high voltage are corrected.
  • the second exposure machine 16 to 21 can advantageously be used, since in this case there is a requirement for extremely high dose constancy during an entire series of exposures.
  • the dose rate can optionally be regulated with the aid of the radiation detectors 8, 16.
  • each of these radiation detectors 8, 16 is followed by a dose rate regulator and an actuator for the dose rate.
  • a radiation detector 8, 16 is optionally connected to the dose rate controller, optionally with the interposition of a transmitter.
  • the dose rate on the X-ray tube 1 is recorded and stored. The saved value then serves as the setpoint after switching. If two dose rate controllers are provided, one of these dose rate controllers is optionally connected to the actuator.
  • a switch 23 is closed to generate a signal proportional to brightness, which bridges the integrator 11. Furthermore, a switch 24 for bridging the integrator 18 is also closed. The dose rate is controlled by an actuator 25 which is switched on by a switch 26.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Toxicology (AREA)
  • X-Ray Techniques (AREA)
  • Apparatus For Radiation Diagnosis (AREA)

Description

Die Erfindung betrifft eine Röntgendiagnostikanlage mit einem Regelkreis, der einen Strahlendetektor für die Erfassung der mittleren Dosis im Bereich der Dominante und eine Regelstufe aufweist, die mindestens einen Aufnahmewert in Abhängigkeit vom Detektor-Ausgangssignal beeinflußt.The invention relates to an x-ray diagnostic system with a control circuit, which has a radiation detector for detecting the average dose in the dominant region and a control stage which influences at least one recording value as a function of the detector output signal.

Es ist eine Röntgendiagnostikanlage dieser Art bekannt, bei der der Regelkreis einen Integrator für das Signal des Strahlendetektors aufweist und die Regelstufe die Hochspannung an der Röntgenröhre beim Erreichen einer vorbestimmten Dosis pro Bild abschaltet. Ein Regelkreis dieser Art wird als Belichtungsautomat bezeichnet. Bei einer Röntgendiagnostikanlage dieser Art werden in der Regel optimal geschwärzte Röntgenbilder erzielt. Im Fall der Indirekttechnik kann der Belichtungsautomat dabei als Strahlendetektor einen Bildverstärker und einen nachgeschalteten Fotomultiplier aufweisen, der die mittlere Bildhelligkeit im Strahlengang zwischen dem Ausgangsleuchtschirm des Röntgenbildverstärkers und einer Bilderfassungseinrichtung in einem vorbestimmten Bereich erfaßt. Fehlbelichtungen können allerdings dann auftreten, wenn sich der Kontrast in dem vom Strahlendetektor erfaßten Bereich während der Serie ändert. Solche Fehlbelichtungen ergeben sich z. B., wenn ein Röntgenkontrastmittel in dem erfaßten Bereich einströmt, denn auch in diesem Fall wird die mittlere Bildheiligkeit konstant gehalten, die aufgrund der hohen Strahlenabsorption des Kontrastmittels erheblich von einem diagnostisch sinnvollen Wert abweichen kann.An X-ray diagnostic system of this type is known, in which the control circuit has an integrator for the signal of the radiation detector and the control stage switches off the high voltage on the X-ray tube when a predetermined dose per image is reached. A control circuit of this type is called an exposure machine. With an X-ray diagnostic system of this type, optimally blackened X-ray images are generally obtained. In the case of indirect technology, the automatic exposure device can have an image intensifier and a downstream photomultiplier as the radiation detector, which detects the average image brightness in the beam path between the exit fluorescent screen of the X-ray image intensifier and an image capturing device in a predetermined range. However, incorrect exposures can occur if the contrast in the area detected by the radiation detector changes during the series. Such incorrect exposures arise e.g. B. when an X-ray contrast agent flows into the detected area, because even in this case the mean image sanctity is kept constant, which can deviate significantly from a diagnostically meaningful value due to the high radiation absorption of the contrast agent.

Der Erfindung liegt die Aufgabe zugrunde, eine Röntgendiagnostikanlage der eingangs genannten Art so auszubilden, daß auch bei einer großen Kontraständerung in dem vom Strahlendetektor erfaßten Bereich eine optimale Bildschwärzung bzw. Helligkeit erzielt wird.The invention has for its object to provide an X-ray diagnostic system of the type mentioned in such a way that optimum image blackening or brightness is achieved even with a large change in contrast in the area detected by the radiation detector.

Diese Aufgabe ist erfindungsgemäß dadurch gelöst, daß ein röhrennaher zweiter Strahlendetektor vorhanden ist, dem ein Speicher für ein von der jeweiligen Dosisleistung beim letzten Bild abhängiges Signal nachgeschaltet ist, daß das Speichersignal als Referenzsignal einer zweiten Regelstufe zugeführt ist und daß ein Umschalter vorhanden ist, durch den die erste Regelstufe ab-und die zweite Regelstufe einschaltbar ist, der dann an einem zweiten Eingang ein vom aktuellen Ausgangssignal des zweiten Strahlendetektors abhängiges Signal zuführbar ist. Bei der erfindungsgemäßen Röntgendiagnostikanlage wird in dem Fall, in dem aufgrund einer hohen Bildkontraständerung aufgrund einströmenden Kontrastmittels in dem vom ersten Strahlendetektor erfaßten Bildbereich Fehlbelichtungen auftreten würden, auf einen vor dem Patienten liegenden zweiten Strahlendetektor umgeschaltet, der auch vor der Umschaltung bereits ein Ausgangssignal liefert. Mit diesem Ausgangssignal wird in einem Speicher ein Signal gebildet, das der Dosis des jeweils letzten durch den ersten Strahlendetektor geschalteten Bildes nach Abschluß des Einregelvorganges der erforderlichen Dosis entspricht. Nach der Umschaltung wird diese Dosis während der gesamten Bildserie konstant gehalten, was zu einer optimalen Bildschwärzung auch nach der Umschaltung führt, denn es ist davon auszugehen, daß sich die für eine optimale Bildschwärzung erforderliche Dosis nicht ändert.This object is achieved in that a tube-near second radiation detector is provided, which is followed by a memory for a signal dependent on the dose rate in the last image, that the memory signal is fed as a reference signal to a second control stage and that a changeover switch is present which the first control stage can be switched off and the second control stage can be switched on, to which a signal dependent on the current output signal of the second radiation detector can then be fed at a second input. In the case of the x-ray diagnostic system according to the invention, in the event that incorrect exposures would occur in the image area detected by the first radiation detector due to a high change in image contrast due to the inflowing contrast medium, a switch is made to a second radiation detector located in front of the patient, which also delivers an output signal before the switchover. With this output signal, a signal is formed in a memory which corresponds to the dose of the last image switched by the first radiation detector after the adjustment process of the required dose has been completed. After the switchover, this dose is kept constant throughout the entire image series, which leads to optimal image blackening even after the switchover, because it can be assumed that the dose required for optimal image blackening does not change.

Die Erfindung ist nachfolgend anhand eines in der Zeichnung dargestellten Ausführungsbeispieles näher erläutert.The invention is explained below with reference to an embodiment shown in the drawing.

In der Zeichnung ist eine Röntgenröhre 1 dargestellt, die von einem Röntgengenerator 2 gespeist wird und einen Patienten 3 durchstrahlt. Die Röntgenbilder werden zunächst auf dem Eingangsleuchtschirm eines Röntgenbildverstärkers 4 erzeugt, dessen Ausgangsbild über eine Fernsehkamera 5 aufgenommen und auf einem Montior 6 wiedergegeben wird. Ferner kann das Ausgangsbild des Röntgenbildverstärkers 4 mit Hilfe einer Filmkamera 7 festgehalten werden.In the drawing, an X-ray tube 1 is shown, which is fed by an X-ray generator 2 and shines through a patient 3. The x-ray images are first generated on the input fluorescent screen of an x-ray image intensifier 4, the output image of which is recorded by a television camera 5 and displayed on a montior 6. Furthermore, the output image of the X-ray image intensifier 4 can be captured using a film camera 7.

Für die automatische Belichtung der Röntgenaufnahmen der Filmkamera 7 ist ein Strahlendetektor 8 vorhanden, der die mittlere Bildhelligkeit in einem vorbestimmten Bereich erfaßt. Hierzu ist ein halbdurchlässiger Spiegel 9 im Strahlengang zwischen dem Ausgangsleuchtschirm des Röntgenbildverstärkers 4 und der Fernsehkamera 5 vorgesehen. Ein weiterer halbdurchlässiger Spiegel 10 führt das Röntgenbild der Filmkamera 7 zu.For the automatic exposure of the X-ray images of the film camera 7, a radiation detector 8 is provided, which detects the average image brightness in a predetermined range. For this purpose, a semi-transparent mirror 9 is provided in the beam path between the exit fluorescent screen of the X-ray image intensifier 4 and the television camera 5. Another semitransparent mirror 10 supplies the x-ray image to the film camera 7.

Das Ausgangssignal des Fotomultiplier 8 wird über einen Strom-Spannungswandler 10 in eine entsprechende Spannung umgewandelt, die in einem Integrator 11 integriert wird. Am Eingang 12 einer Schaltstufe 13 liegt demgemäß ein Signal, das der für ein Bild aufgelaufenen Dosis entspricht. Am Eingang 14 der Schaltstufe 13 wird ein Referenzsignal angelegt. Sobald das Signal am Eingang 12 das Signal am Eingang 14 erreicht, bewirkt die Schaltstufe 13 über den Schalter 15, der zunächst seine voll gezeichnete Stellung einnimmt, die Abschaltung der Röntgenröhrenspannung 1.The output signal of the photomultiplier 8 is converted via a current-voltage converter 10 into a corresponding voltage, which is integrated in an integrator 11. Accordingly, there is a signal at the input 12 of a switching stage 13 which corresponds to the dose accumulated for an image. A reference signal is applied to input 14 of switching stage 13. As soon as the signal at the input 12 reaches the signal at the input 14, the switching stage 13 switches off the X-ray tube voltage 1 via the switch 15, which initially assumes its fully drawn position.

Die dargestellte Röntgendiagnostikanlage weist einen zweiten, röhrennahen Strahlendetektor 16 auf, dessen Ausgangssignal über einfn Strom-Spannungswandler 17 in eine entsprechende Spannung umgewandelt wird, die in einem Integrator 18 integriert wird. Das Ausgangssignal des Integrators 18 wird über einen zunächst seine voll gezeichnete Stellung einnehmenden Schalter 19 in einem Speicher 20 integriert und als Referenzspannung einer zweiten Schaltstufe 21 zugeführt.The X-ray diagnostic system shown has a second, near-tube radiation detector 16, the output signal of which is converted via a current-voltage converter 17 into a corresponding voltage, which is integrated in an integrator 18. The output signal of the integrator 18 is integrated in a memory 20 via a switch 19 which initially assumes its fully drawn position and is supplied as a reference voltage to a second switching stage 21.

Stellt der Benutzer der Röntgendiagnostikanlage fest, daß der Kontrast in dem diagnostisch relevanten Bildbereich zu groß wird, beispielsweise weil ein Kontrastmittel dort ankommt, so betätigt er die Schalter 15, 19 und legt sie in ihre gestrichelt gezeichneten Stellungen um. Dieser Vorgang kann auch nach Ablauf einer Testserie automatisch erfolgen. Der Schalter 15 trennt dabei den Ausgang der Schaltstufe 13 vom Röntgengenerator 2 ab und schaltet dafür den Ausgang der Schaltstufe 21 an. Der Schalter 19 führt das Ausgangssignal des Integrators 18 als Istwerts gnal der Schaltstufe 21 zu. Das Sollwertsignal ist die Referenzspannung, die vom Speicher 20 geliefert wird. Der Speicher 20 liefert dabei eine Referenzspannung, die der beim letzten Bild vor Betätigung der Schalter 15, 19 erreichten Dosis entspricht. Er wird vor dieser Betätigung nach jedem durch den Belichtungsautomaten 8 bis 13 geschalteten Bild zurückgestellt. Dies gilt auch für den Integrator 18.If the user of the X-ray diagnostic system determines that the contrast in the diagnostically relevant image area is too high, for example because a contrast medium is arriving there, he actuates the switches 15, 19 and switches them to their positions shown in dashed lines. This process can also be carried out after a series of tests done automatically. The switch 15 separates the output of the switching stage 13 from the X-ray generator 2 and switches the output of the switching stage 21 on. The switch 19 feeds the output signal of the integrator 18 to the switching stage 21 as an actual value signal. The setpoint signal is the reference voltage that is supplied by the memory 20. The memory 20 supplies a reference voltage which corresponds to the dose reached in the last picture before the switches 15, 19 were actuated. Before this actuation, it is reset after each image switched by the exposure machine 8 to 13. This also applies to the integrator 18.

Nach Übergang auf den Belichtungsautomaten 16 bis 21 werden demgemäß die Bilder automatisch mit einer Dosis geschaltet, die bei dem letzten durch den Belichtungsautomaten 8 bis 13 geschalteten Bild einer Testserie erreicht wurde und die demgemäß zu einer optimalen Bildschwärzung führt. Die Ankunft eines Kontrastmittels in dem untersuchten Bereich ist dabei ohne Auswirkung auf das Ausgangssignal des Strahlendetektors 16 und damit auf die Bildschwärzung.After the transition to the automatic exposure devices 16 to 21, the images are accordingly switched automatically with a dose which was achieved in the last image of a test series switched by the automatic exposure devices 8 to 13 and which accordingly leads to an optimal image blackening. The arrival of a contrast medium in the examined area has no effect on the output signal of the radiation detector 16 and thus on the image blackening.

Durch den Belichtungsautomaten 16 bis 21 ist erreicht, daß insbesondere auch dann, wenn der Belichtungsautomat 8 bis 13 abgeschaltet ist, Netzspannungsschwankungen, Änderungen des Röntgenröhrenstromes bei unverändertem Einstellwert (Rückwirkung der Anode), Schwebungserscheinungen bei nicht netzsynchronem Takt einer Aufnahmeserie, bei der die Röntgenröhre 1 gepulst wird, und Einflüsse von Einschwingvorgängen der Röntgenröhren-Hochspannung ausgeregelt werden. Insbesondere bei der digitalen Subtraktionsangiographie ist der zweite Belichtungsautomat 16 bis 21 mit Vorteil anwendbar, da in diesem Fall die Forderung nach extrem hoher Dosiskonstanz während einer gesamten Aufnahmeserie besteht.By means of the automatic exposure device 16 to 21 it is achieved that, particularly when the automatic exposure device 8 to 13 is switched off, mains voltage fluctuations, changes in the X-ray tube current with unchanged setting value (reaction of the anode), beat phenomena with a cycle of the recording in which the X-ray tube 1 is not synchronized with the network is pulsed, and influences of transient processes of the X-ray tube high voltage are corrected. In the case of digital subtraction angiography in particular, the second exposure machine 16 to 21 can advantageously be used, since in this case there is a requirement for extremely high dose constancy during an entire series of exposures.

Wird die Röntgenröhrenspannung nicht gepulst, sondern kontinuierlich eingeschaltet (Durchleuchtung), so kann mit Hilfe der Strahlendetektoren 8, 16 wahlweise die Dosisleistung geregelt werden. In diesem Fall ist jedem dieser Strahlendetektoren 8, 16 ein Dosisleistungsregier und ein Stellglied für die Dosisleistung nachgeschaltet. Bei Vewendung eines gemeinsamen Dosisleistungsreglers wird jeweils ein Strahlendetektor 8, 16 wahlweise, gegebenenfalls unter Zwischenschaltung eines Meßumformers, an den Dosisleistungsregler angeschaltet. Während der Einregelphase wird dabei die Dosisleistung an der Röntgenröhre 1 erfaßt und abgespeichert. Der gespeicherte Wert dient dann nach Umschaltung als Sollwert. Sind zwei Dosisleistungsregler vorgesehen, so wird wahlweise je einer dieser Dosisleistungsregler an das Stellglied angeschaltet.If the x-ray tube voltage is not pulsed but switched on continuously (fluoroscopy), the dose rate can optionally be regulated with the aid of the radiation detectors 8, 16. In this case, each of these radiation detectors 8, 16 is followed by a dose rate regulator and an actuator for the dose rate. When a common dose rate controller is used, a radiation detector 8, 16 is optionally connected to the dose rate controller, optionally with the interposition of a transmitter. During the regularization phase, the dose rate on the X-ray tube 1 is recorded and stored. The saved value then serves as the setpoint after switching. If two dose rate controllers are provided, one of these dose rate controllers is optionally connected to the actuator.

Für die Dosisleistungsregelung wird ein Schalter 23 zur Erzeugung eines helligkeitsproportionalen Signales geschlossen, der den Integrator 11 überbrückt. Ferner wird auch ein Schalter 24 zur Überbrückung des Integrators 18 geschlossen. Die Dosisleistungsregelung erfolgt durch ein Stellglied 25, das durch einen Schalter 26 eingeschaltet wird.For dose rate control, a switch 23 is closed to generate a signal proportional to brightness, which bridges the integrator 11. Furthermore, a switch 24 for bridging the integrator 18 is also closed. The dose rate is controlled by an actuator 25 which is switched on by a switch 26.

Claims (2)

1. An X-ray diagnostic apparatus comprising a regulating circuit (8 to 13) including a radiation detector (8) to detect the mean dose in the dominant range and a regulating stage (13) to influence at least one recorded value in dependence upon the detector output signal, characterised in that a second radiation detector (16) is arranged close to the tube and has its output connected to a store (20) for a signal dependent upon the respective dose value of the last image, and this stored signal is supplied as a reference signal to a second regulating stage (21), a change-over switch (15, 19) being provided which switches off the first regulating stage (13) and switches on the second regulating stage (21) so that a second input (22) can then be supplied with a signal dependent upon the current output signal of the second radiation detector (16).
2. An X-ray diagnostic apparatus as claimed in Claim 1, characterised in that the regulating circuit (8 to 13) includes an integrator (11) for the signal of the first radiation detector (8) and that the regulating stage (13) disconnects the high voltage from the X-ray tube (1) when a predetermined dose is achieved in respect of each image, that the second radiation detector (16) is connected to a second integrator (18) whose output is connected to the store (20), and that when the change-over switch (15, 19) is actuated, the second input (22) of the second regulating stage (21) is supplied with the output signal of the second integrator (18).
EP84115058A 1984-01-27 1984-12-10 X-ray diagnostic apparatus Expired EP0151270B1 (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE3402888 1984-01-27
DE19843402888 DE3402888A1 (en) 1984-01-27 1984-01-27 X-RAY DIAGNOSTIC SYSTEM

Publications (2)

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EP0151270A1 EP0151270A1 (en) 1985-08-14
EP0151270B1 true EP0151270B1 (en) 1987-09-30

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JP (1) JPS60140399U (en)
DE (2) DE3402888A1 (en)

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DE3466638D1 (en) 1987-11-05
JPS60140399U (en) 1985-09-17
EP0151270A1 (en) 1985-08-14
US4639943A (en) 1987-01-27
DE3402888A1 (en) 1985-08-01

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