EP0416708B1 - Générateur à rayons X pour le fonctionnement d'un tube à rayons X dont les parties sont mises à la masse - Google Patents

Générateur à rayons X pour le fonctionnement d'un tube à rayons X dont les parties sont mises à la masse Download PDF

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Publication number
EP0416708B1
EP0416708B1 EP90202356A EP90202356A EP0416708B1 EP 0416708 B1 EP0416708 B1 EP 0416708B1 EP 90202356 A EP90202356 A EP 90202356A EP 90202356 A EP90202356 A EP 90202356A EP 0416708 B1 EP0416708 B1 EP 0416708B1
Authority
EP
European Patent Office
Prior art keywords
voltage
inductance
cathode
ray
windings
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.)
Expired - Lifetime
Application number
EP90202356A
Other languages
German (de)
English (en)
Other versions
EP0416708A3 (en
EP0416708A2 (fr
Inventor
Hans Dipl.-Ing. Negle
Bernd Freiheit-Jensen
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Philips Intellectual Property and Standards GmbH
Koninklijke Philips NV
Original Assignee
Philips Patentverwaltung GmbH
Koninklijke Philips Electronics NV
Philips Electronics NV
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 Patentverwaltung GmbH, Koninklijke Philips Electronics NV, Philips Electronics NV filed Critical Philips Patentverwaltung GmbH
Publication of EP0416708A2 publication Critical patent/EP0416708A2/fr
Publication of EP0416708A3 publication Critical patent/EP0416708A3/de
Application granted granted Critical
Publication of EP0416708B1 publication Critical patent/EP0416708B1/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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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
    • H05G1/10—Power supply arrangements for feeding the X-ray tube

Definitions

  • the invention relates to an X-ray generator according to the preamble of claim 1.
  • Such an X-ray generator is known from FR-A-2 527 035.
  • the current generated at the cathode does not flow completely to the anode; part of this current flows to ground via the relevant tube part.
  • the cathode-side high-voltage source is subjected to greater stress than the anode-side high-voltage source, which in the case of high-resistance, symmetrically designed high-voltage sources leads to an asymmetry between the high voltage at the anode or at the cathode (i.e. the high voltage between the anode and ground is greater than the high voltage between the cathode and Dimensions).
  • the voltage asymmetry and the resulting negative effects are eliminated in that a special inverter is provided which can be operated in such a way that the electrical power supplied via the primary and secondary windings for the cathode voltage becomes greater than that via the primary - And secondary windings for the anode voltage supplied electrical power.
  • each secondary winding is also assigned a primary winding, so that the voltages on the secondary windings can be predetermined independently of one another, at least in a certain range. If one assumes that the primary windings correspond to one another and also the secondary windings, then the X-ray generator according to the invention delivers to a "normal" X-ray tube, i.e. an X-ray tube without tube parts connected to ground, e.g. an X-ray tube with a glass bulb, a symmetrical voltage distribution, i.e. the amount of voltage between the anode and ground is the same as the voltage between cathode and ground.
  • a "normal" X-ray tube i.e. an X-ray tube without tube parts connected to ground, e.g. an X-ray tube with a glass bulb
  • a symmetrical voltage distribution i.e. the amount of voltage between the anode and ground is the same as the voltage between cathode and ground.
  • the inductance is connected in series with the primary winding for generating the high voltage on the anode side by means of the switching device.
  • the voltage on the anode-side primary winding is reduced in comparison to the voltage on the cathode-side primary voltage, as a result of which, when the inductance is suitably dimensioned, the anode voltage is reduced at least approximately by the same amount as the cathode voltage as a result of the higher cathode current.
  • the inductance such that the anode voltage drops more than the cathode voltage, so that the cathode voltage is greater than half the tube voltage - as long as the cathode voltage does not exceed half the maximum tube voltage.
  • the space charge in the region of the cathode can be eliminated, so that the current through the X-ray tube increases or at a given cathode temperature given tube current, the cathode temperature is lowered and the life of the cathode can be increased.
  • a preferred embodiment therefore provides that the primary windings and the secondary windings are wound on a common core and are arranged in such a way that the leakage inductance between the mutually assigned primary and secondary windings is substantially smaller than the leakage inductance between the windings which are not assigned to one another.
  • the inductor consists of several partial inductors lying in series and that a switchover device can be coupled to the partial inductors in such a way that the inductor can be switched completely or only partially into the feed line to the primary winding.
  • This configuration allows the (partial) inductance connected in series with the anode-side primary winding to be adapted to the respective requirements in stages: at high tube voltages, a relatively small partial inductance is switched on by means of the switching device, which is dimensioned such that the anode and cathode voltage are at least approximately are equal in amount.
  • a larger inductance is made effective, so that the cathode voltage becomes greater than the anode voltage, which makes it possible to lower the cathode temperature for a given tube current.
  • the inductance is designed as an air throttle.
  • the inductance could also be formed by a coil with a ferromagnetic core.
  • the inductances required are relatively small, such a coil would have only one or a few turns, so that exact dimensioning would be difficult.
  • saturation phenomena would occur with such a coil because of the high currents which can flow through the primary winding in an X-ray image (a few hundred A).
  • an air choke ie a coil without a ferromagnetic core, can have a sufficient number of turns and shows no saturation effects.
  • the inductor is wound on a toroid.
  • An air throttle could in itself be wound particularly easily on a cylinder core.
  • An air choke with turns evenly distributed around the circumference of the (non-ferromagnetic) ring core is more difficult to wind, but it creates a smaller magnetic stray field in its environment.
  • X-ray tubes 1 and 2 optionally connectable to the X-ray generator are provided. While the x-ray tube 2 has the same cathode current as the anode current because this tube has a glass bulb, for example, this is not the case with the x-ray tube 1. As indicated schematically, this X-ray tube has a grounded metal piston and a central part connected to it in an electrically conductive manner and arranged between the anode and cathode. In such an x-ray tube known per se (see also EP-OS 74 141), part of the cathode current can flow to earth via the central part and the metal bulb, so that the cathode current is greater than the anode current.
  • One of the two X-ray tubes 1 or 2 each located at different workplaces (in clinical practice, even more X-ray tubes can be provided) can be connected to the high voltage generated in the X-ray generator by means of a high-voltage switchover device 3 - which can be coupled with the workstation selector (not shown).
  • the high voltage for the rectifiers 11 and 12 is supplied by the secondary windings 21 and 22, to which a primary winding 31 and 32 is assigned.
  • the four windings mentioned are wound on a common transformer core 4.
  • a secondary winding arrangement consisting of several individual windings can also be used.
  • the output voltage of the rectifiers 11 and 12 is smoothed by capacitors 41 and 42 and fed to the changeover switch 3 via a damping resistor 51 and 52, respectively.
  • the positive or negative high voltage, to which one of the X-ray tubes 1 or 2 is connected in the operating state, is detected by a voltage divider 61 or 62 for measurement and control purposes.
  • FIG. 2 shows a cross section through the high-voltage transformer with the core 4, the two primary windings 31 and 32 and the two secondary windings 21 and 22.
  • the core 4 a cutting tape core, has the shape of a rectangular ring core.
  • Such a core is expediently composed of two identical cores with a U-shape, so that the windings can be produced before they are each applied to one core and before the two cores are assembled.
  • the secondary windings 21 and 22 each enclose the primary winding 31 and 32 assigned to them, and the primary windings 31 and 32 enclose the same leg of the core 4. Since the primary windings have the same number of turns - and likewise the secondary windings - this results in a transformer structure that is symmetrical with respect to the center line 40.
  • the magnetic coupling between mutually unassigned windings - for example the primary winding 32 and the secondary winding 21 is considerably weaker - and accordingly the leakage inductance or the leakage induction flux is considerably greater - than between the mutually associated windings, for example the primary winding 31 and Secondary winding 21.
  • a ratio of the mentioned leakage inductances of 6: 1 has already proven to be sufficient to enable the windings to be fed asymmetrically without inadmissibly high equalizing currents flowing.
  • the two primary windings 31 and 32 are fed by a controllable AC voltage source, for example with a medium-frequency series resonance inverter with an operating frequency of e.g. 3-12 kHz.
  • a controllable AC voltage source for example with a medium-frequency series resonance inverter with an operating frequency of e.g. 3-12 kHz.
  • an inductor is provided in one of the connecting lines between the primary winding 31 and the AC voltage generator, which consists of the partial inductors 7, 8 and 9 connected in series. which each have a switch 70, 80 and 90 connected in parallel.
  • the primary and secondary windings must be arranged in a boiler filled with transformer oil, for example, the partial inductors 7, 8 and 9 and the switches 70, 80 and 90 can be arranged outside of this boiler.
  • the x-ray generator is operated as follows: when the x-ray tube 2 is connected (in the extended position of the high-voltage switch 3), all the switches 70, 80 and 90 closed so that the inductance 7, 8, 9 is short-circuited.
  • the primary windings 31 and 32 are fed with alternating voltages of the same size, so that there is a symmetrical voltage distribution on the X-ray tube 2, ie the amount of the anode is the same as the cathode voltage (in each case with respect to ground or ground).
  • the high-voltage switch 3 is switched to the position not shown in FIG. 1.
  • only one switch is opened in this case, for example switch 70, so that only partial inductance 7 in series with primary winding 31 is effective.
  • the voltage across the primary winding 31 is less than that across the primary winding 32 and, accordingly, the open circuit voltage (ie, the voltage under no load from the X-ray tube 1) is lower than the open circuit voltage at the output of the rectifier 12.
  • the operating voltage at the cathode drops more than at the anode, so that, with suitable dimensioning of the partial inductance 7, a symmetrical voltage distribution at the x-ray tube 1 arises at least approximately.
  • the switches 70, 80, 90 must be controlled as a function of the voltage on the X-ray tube. If, on the other hand, there is only a single switch and only a single inductance, the switch is controlled as a function of the workplace selector (not shown in more detail) which also operates the high-voltage switch 3.

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  • X-Ray Techniques (AREA)

Claims (5)

  1. Générateur de rayons X comportant un tube à rayons X (1) avec des parties de tube mises à la masse et un montage de transformateur haute tension avec un montage d'enroulements primaire (31) et secondaire (21) pour produire la tension anodique pour le tube à rayons X et un montage d'enroulements primaire (32) et secondaire (22) pour produire la tension cathodique pour le tube à rayons X, caractérisé en ce qu'une inductance (7, 8, 9) peut être connectée au moyen d'un dispositif de commutation (70, 80, 90) en série avec l'enroulement primaire (31) pour la production de la tension anodique.
  2. Générateur de rayons X selon la revendication 1, caractérisé en ce que les enroulements primaires (31, 32) et les enroulements secondaires (21, 22) sont bobinés sur un noyau commun (4) et sont agencés, de telle sorte que l'inductance de fuite entre les enroulements primaires et secondaires conjugués (par exemple 31, 21) soit sensiblement plus petite que l'inductance de fuite entre les enroulements non conjugués (par exemple 31, 22).
  3. Générateur de rayons X selon l'une quelconque des revendications précédentes, caractérisé en ce que l'inductance est constituée de plusieurs inductances partielles connectées en série (7, 8, 9) et en ce qu'un dispositif de commutation (70, 80, 90) peut être connecté aux inductances partielles, de telle sorte que l'inductance puisse être commutée dans sa totalité ou seulement partiellement dans la ligne d'alimentation de l'enroulement primaire (31).
  4. Générateur de rayons X selon l'une quelconque des revendications précédentes, caractérisé en ce que l'inductance (7, 8, 9) est conçue sous la forme d'une bobine de self à air.
  5. Générateur de rayons X selon la revendication 4, caractérisé en ce que l'inductance (7, 8, 9) est bobinée sur un noyau annulaire.
EP90202356A 1989-09-08 1990-09-05 Générateur à rayons X pour le fonctionnement d'un tube à rayons X dont les parties sont mises à la masse Expired - Lifetime EP0416708B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE3929888A DE3929888A1 (de) 1989-09-08 1989-09-08 Roentgengenerator zum betrieb einer roentgenroehre mit an masse angeschlossenen roehrenteilen
DE3929888 1989-09-08

Publications (3)

Publication Number Publication Date
EP0416708A2 EP0416708A2 (fr) 1991-03-13
EP0416708A3 EP0416708A3 (en) 1991-08-07
EP0416708B1 true EP0416708B1 (fr) 1995-03-15

Family

ID=6388914

Family Applications (1)

Application Number Title Priority Date Filing Date
EP90202356A Expired - Lifetime EP0416708B1 (fr) 1989-09-08 1990-09-05 Générateur à rayons X pour le fonctionnement d'un tube à rayons X dont les parties sont mises à la masse

Country Status (4)

Country Link
US (1) US5123038A (fr)
EP (1) EP0416708B1 (fr)
JP (1) JP2970930B2 (fr)
DE (2) DE3929888A1 (fr)

Families Citing this family (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE4021585A1 (de) * 1990-07-06 1992-01-09 Philips Patentverwaltung Hochspannungstransformator, insbesondere fuer ein roentgengeraet
FR2680939B1 (fr) * 1991-09-03 1993-11-26 General Electric Cgr Sa Dispositif et bloc d'alimentation haute tension pour tube a rayons x.
JP2634369B2 (ja) * 1993-07-15 1997-07-23 浜松ホトニクス株式会社 Ｘ線装置
US5490196A (en) * 1994-03-18 1996-02-06 Metorex International Oy Multi energy system for x-ray imaging applications
DE4443551A1 (de) * 1994-12-07 1996-06-20 Philips Patentverwaltung Anordnung zur Leistungsversorgung eines elektrischen Verbrauchers, insbesondere Röntgen-Apparat
DE19631143C2 (de) * 1996-08-01 2003-03-20 Siemens Ag Hochfrequenz-Röntgengenerator
DE19645418A1 (de) * 1996-11-04 1998-05-07 Siemens Ag Hochfrequenz-Röntgengenerator
DE10025807A1 (de) * 2000-05-24 2001-11-29 Philips Corp Intellectual Pty Röntgenröhre mit Flachkathode
ES2172458B1 (es) * 2001-01-10 2003-12-16 Es De Electromedicina Y Calida Transformador de alta tension.
JP2003142294A (ja) * 2001-10-31 2003-05-16 Ge Medical Systems Global Technology Co Llc 高電圧発生回路およびｘ線発生装置
US7903432B2 (en) 2009-05-29 2011-03-08 General Electric Company High-voltage power generation system and package
JP5979827B2 (ja) * 2011-07-27 2016-08-31 株式会社日立製作所 インバータ式ｘ線高電圧装置
JP6532233B2 (ja) * 2015-01-07 2019-06-19 キヤノン株式会社 絶縁トランス及びそれを備えた放射線発生装置、放射線撮影システム
EP3562275B1 (fr) 2018-04-23 2020-04-08 Siemens Healthcare GmbH Transformateur haute tension
CN119184729A (zh) * 2024-09-20 2024-12-27 武汉联影医疗科技有限公司 X射线管的负载均衡方法和负载均衡的x射线系统

Family Cites Families (11)

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Publication number Priority date Publication date Assignee Title
US2530188A (en) * 1946-12-07 1950-11-14 Westinghouse Electric Corp Load reading voltmeter
NL88026C (nl) * 1953-03-21 1958-05-16 Philips Nv roentgentoestel met wisselstroomvoeding voor het maken van roentgenfoto'smet trapsgewijze instelbare belichtingstijden
GB761705A (en) * 1954-03-26 1956-11-21 Gotfred Borge Davidsen Electric supply circuit for the operation of x-ray tubes
NL103475C (nl) * 1954-11-03 1963-01-15 Philips Nv roentgentoestel
DE2053606A1 (de) * 1970-10-31 1972-05-10 Mueller C H F Gmbh Einrichtung zur selbsttätigen Einstellung der Brennfleckgröße einer Röntgenröhre in Abhängigkeit von der Röhrenbelastung
DE2820773A1 (de) * 1978-05-12 1979-11-15 Ritter Ag Roentgengeraet
DE3046413A1 (de) * 1980-12-10 1982-07-29 Philips Patentverwaltung Gmbh, 2000 Hamburg "roentgendiagnostikgenerator"
DE3135061A1 (de) * 1981-09-04 1983-03-24 Philips Patentverwaltung Gmbh, 2000 Hamburg Roentgengenerator zum betrieb von roentgenroehren mit an masse angeschlossenem mittelteil
DE3218535A1 (de) * 1982-05-17 1983-11-17 Philips Patentverwaltung Hochspannungserzeuger, insbesondere zur speisung einer roentgenroehre
DE3437064A1 (de) * 1984-10-09 1986-04-10 Siemens AG, 1000 Berlin und 8000 München Mittelfrequenz-roentgengenerator
DE3601857A1 (de) * 1986-01-23 1987-07-30 Philips Patentverwaltung Schaltungsanordnung zur hochspannungsstellung

Also Published As

Publication number Publication date
JP2970930B2 (ja) 1999-11-02
DE3929888A1 (de) 1991-03-14
US5123038A (en) 1992-06-16
EP0416708A3 (en) 1991-08-07
EP0416708A2 (fr) 1991-03-13
JPH03101098A (ja) 1991-04-25
DE59008699D1 (de) 1995-04-20

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