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WO2012123232A1 - Ensemble de circuit avec onduleur pour alimenter en tension un tube à rayons x et procédé associé - Google Patents

Ensemble de circuit avec onduleur pour alimenter en tension un tube à rayons x et procédé associé Download PDF

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Publication number
WO2012123232A1
WO2012123232A1 PCT/EP2012/053152 EP2012053152W WO2012123232A1 WO 2012123232 A1 WO2012123232 A1 WO 2012123232A1 EP 2012053152 W EP2012053152 W EP 2012053152W WO 2012123232 A1 WO2012123232 A1 WO 2012123232A1
Authority
WO
WIPO (PCT)
Prior art keywords
voltage
circuit
frequency
ray tube
transformer
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.)
Ceased
Application number
PCT/EP2012/053152
Other languages
German (de)
English (en)
Inventor
Walter Beyerlein
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.)
Siemens AG
Siemens Corp
Original Assignee
Siemens AG
Siemens Corp
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 Siemens AG, Siemens Corp filed Critical Siemens AG
Publication of WO2012123232A1 publication Critical patent/WO2012123232A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

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
    • H05G1/20—Power supply arrangements for feeding the X-ray tube with high-frequency AC; with pulse trains
    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02M—APPARATUS FOR CONVERSION BETWEEN AC AND AC, BETWEEN AC AND DC, OR BETWEEN DC AND DC, AND FOR USE WITH MAINS OR SIMILAR POWER SUPPLY SYSTEMS; CONVERSION OF DC OR AC INPUT POWER INTO SURGE OUTPUT POWER; CONTROL OR REGULATION THEREOF
    • H02M3/00—Conversion of DC power input into DC power output
    • H02M3/01—Resonant DC/DC converters
    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02M—APPARATUS FOR CONVERSION BETWEEN AC AND AC, BETWEEN AC AND DC, OR BETWEEN DC AND DC, AND FOR USE WITH MAINS OR SIMILAR POWER SUPPLY SYSTEMS; CONVERSION OF DC OR AC INPUT POWER INTO SURGE OUTPUT POWER; CONTROL OR REGULATION THEREOF
    • H02M3/00—Conversion of DC power input into DC power output
    • H02M3/22—Conversion of DC power input into DC power output with intermediate conversion into AC
    • H02M3/24—Conversion of DC power input into DC power output with intermediate conversion into AC by static converters
    • H02M3/28—Conversion of DC power input into DC power output with intermediate conversion into AC by static converters using discharge tubes with control electrode or semiconductor devices with control electrode to produce the intermediate AC
    • H02M3/325—Conversion of DC power input into DC power output with intermediate conversion into AC by static converters using discharge tubes with control electrode or semiconductor devices with control electrode to produce the intermediate AC using devices of a triode or a transistor type requiring continuous application of a control signal
    • H02M3/335—Conversion of DC power input into DC power output with intermediate conversion into AC by static converters using discharge tubes with control electrode or semiconductor devices with control electrode to produce the intermediate AC using devices of a triode or a transistor type requiring continuous application of a control signal using semiconductor devices only
    • H02M3/33569—Conversion of DC power input into DC power output with intermediate conversion into AC by static converters using discharge tubes with control electrode or semiconductor devices with control electrode to produce the intermediate AC using devices of a triode or a transistor type requiring continuous application of a control signal using semiconductor devices only having several active switching elements
    • H02M3/33573—Full-bridge at primary side of an isolation transformer
    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02M—APPARATUS FOR CONVERSION BETWEEN AC AND AC, BETWEEN AC AND DC, OR BETWEEN DC AND DC, AND FOR USE WITH MAINS OR SIMILAR POWER SUPPLY SYSTEMS; CONVERSION OF DC OR AC INPUT POWER INTO SURGE OUTPUT POWER; CONTROL OR REGULATION THEREOF
    • H02M1/00—Details of apparatus for conversion
    • H02M1/0048—Circuits or arrangements for reducing losses
    • H02M1/0054—Transistor switching losses
    • H02M1/0058—Transistor switching losses by employing soft switching techniques, i.e. commutation of transistors when applied voltage is zero or when current flow is zero
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
    • Y02B—CLIMATE CHANGE MITIGATION TECHNOLOGIES RELATED TO BUILDINGS, e.g. HOUSING, HOUSE APPLIANCES OR RELATED END-USER APPLICATIONS
    • Y02B70/00—Technologies for an efficient end-user side electric power management and consumption
    • Y02B70/10—Technologies improving the efficiency by using switched-mode power supplies [SMPS], i.e. efficient power electronics conversion e.g. power factor correction or reduction of losses in power supplies or efficient standby modes

Definitions

  • the invention relates to a circuit arrangement for generating an X-ray tube voltage with an input circuit for generating a DC link voltage, with an inverter circuit for converting the DC link voltage into a high-frequency AC voltage and with a high-voltage generator, which converts the high-frequency AC voltage with a certain gear ratio in a high voltage for the X-ray tube. Moreover, the invention relates to an X-ray generator with such a circuit arrangement and to a corresponding method for generating an X-ray tube voltage.
  • Modern generators often have circuit arrangements of the type mentioned for generating an X-ray tube voltage. Since the network frequency is first rectified and then converted back into a high-frequency AC voltage, which is finally trans ⁇ formed to the desired voltage, such generators are also referred to as Hochfre ⁇ frequency generators. Compared with conventional generators, in which the high voltage is first transformed with the present network frequency, then rectified and finally fed to the X-ray tube, such a circuit arrangement has the advantage that they are made almost independent by a fast control loop of changes in both the mains voltage and the tube current can and therefore the tube voltage is very well reproducible and can be kept constant.
  • the high-frequency generators Compared to the well-known so-called DC voltage generators, in which a transformed with line frequency and rectified high ⁇ voltage is finely controlled by means of triodes, the high-frequency generators have the advantage of a relatively small volume and lower manufacturing costs.
  • the circuit arrangements must in this case be dimensioned such that they provide a constant power over a very large voltage range.
  • the voltage range used in medical diagnostics for x-ray tubes usually ranges from 40 kV to 150 kV. In order to deliver constant power over this range, the current at the lowest voltage level of 40 kV must be nearly four times higher than at the upper limit of 150 kV.
  • the high voltage generator must be chosen in its transmission ratio so that the highest required tube voltage is achieved at a given by the available mains voltage DC link voltage.
  • the transmission ratio of the high voltage generator is usually defined in such X-ray generators as the ratio ⁇ nis the output voltage to the input voltage of the high voltage generator.
  • the high-tension voltage generator ⁇ essentially consists of a transformer and a downstream rectifying and smoothing circuit. If it is assumed that the effective voltage is close to the inverter circuit in such as the intermediate circuit voltage corresponds, and that the high-voltage generator is designed so that by a suitable transformer nachge ⁇ switched rectifier circuit, a voltage doubling is achieved, it follows for the transmission ratio ü of the transformer of the high voltage generator:
  • U dc is the rectified DC link voltage and U t is the voltage applied to the X-ray tube, rectified high ⁇ voltage.
  • I t is therefore consequently the average current I avg strain WR for the primary side of the high voltage generator and the front switched AC Rich ⁇ tersctreu
  • the object is achieved with the scarf ⁇ processing arrangement and the method of the independent claims.
  • the invention claims a circuit arrangement for generating an X-ray tube voltage with a mains input circuit for generating a DC link voltage, with an inverter circuit for converting the DC link voltage into a high-frequency AC voltage and with a high voltage generator, which converts the high-frequency AC voltage into a high voltage for the X-ray tube, wherein the high voltage generator is a transformer and a high-voltage capacitor connected in parallel with the secondary winding of the transformer, which together with the in productivity of the secondary winding forms a resonant circuit, which has its resonance frequency in the frequency range between 10 kHz and 50 kHz.
  • the invention offers the advantage that the existing parasitic winding capacitance of the transformer is optionally increased by an additional capacitor to the extent that it can be used as a useful component for increasing the voltage of a high voltage source. This allows the inverter to be designed for smaller currents. Also, the transmission power between the inverter and transformer are relieved.
  • the capacitance of the high-voltage capacitor can be selected such that at a predeterminable operating point of the X-ray tube at the resonance ⁇ frequency of the AC voltage, the voltage at the X-ray tube at least doubles.
  • the invention also claims a circuit arrangement for generating an X-ray tube voltage with a mains input circuit for generating a DC link voltage, an inverter circuit for converting the DC link voltage into a high-frequency AC voltage and a high voltage generator, which converts the high-frequency AC voltage into a high voltage for the X-ray tube, wherein the high voltage generator comprises a transformer and one to the primary winding of the transformer connected in parallel resonant circuit capacitor and one to the primary winding and the
  • Resonant circuit capacitor connected in series Schwingschispu ⁇ le which forms a resonant circuit, which has its resonant frequency in the frequency ⁇ range between 10 kHz and 500 kHz.
  • the capacitance of the resonant circuit capacitor and the inductance of the resonant ⁇ circuit coil may be chosen such that the voltage at the X-ray tube at least doubled for a predeterminable operating point of the X-ray tube at the resonant frequency of the AC voltage.
  • the invention also claims an X-ray device with an X-ray generator according to the invention.
  • the invention also claims a method of generating an X-ray tube voltage in which an intermediate circuit voltage is generated from a mains input voltage and a high-frequency alternating voltage is generated from the intermediate circuit voltage, which is converted into a high voltage for the X-ray tube by means of a high voltage generator with a transformer Secondary winding of the transformer pa ⁇ rallel switched high voltage capacitor is brought together with the inductance of the secondary winding in the frequency range between 10 kHz and 500 kHz in resonance.
  • the invention further claims a method for generating an X-ray tube voltage in which generates a DC link voltage from a mains input voltage and from the DC link voltage, a high-frequency AC voltage is converted with a high voltage generator with a transformer in a high voltage for the X-ray tube, wherein a Primary winding of Trans ⁇ formator connected in parallel resonant circuit capacitor together with a primary winding and the resonant circuit capacitor connected in series resonant circuit coil in the frequency range between 10 kHz and 500 kHz are brought into resonance.
  • the method of the X-ray tube in the Reso can ⁇ nanzfrequenz the voltage at the X-ray tube be at least doubled at a predeterminable operating point.
  • Figure 1 a block diagram of a circuit arrangement for
  • Figure 2 is a block diagram of a circuit arrangement for
  • FIG. 3 shows a block diagram of a circuit arrangement for
  • FIG. 4 shows a diagram of the tube voltage as a function of the inverter frequency for different tube currents
  • Figure 5 is a block diagram of a high voltage generator
  • FIG. 6 shows a block diagram of another high-voltage ⁇ creator.
  • the network input side includes a network input circuit 1, which generates a rectified intermediate circuit voltage U dC from the two- or three-phase input voltage.
  • This rectified intermediate circuit voltage U DC is then applied to the input of an inverter circuit 2 that converts the intermediate circuit voltage U DC into a high-frequency AC voltage clamping ⁇ .
  • a rectangular inverter is shown. Instead of egg nes such rectangle inverter are often used Schwing ⁇ circular inverters.
  • the present at the output of the inverter circuit 2, high-frequency alternating voltage is then forwarded to a high voltage generator 6, which consists essentially of a transformer 3 and the transformer 3 on the secondary side rectifying rectified and smoothing device 4.
  • the rectifying and smoothing device 4 is often designed as a doubler circuit.
  • the applied at the output of the high voltage generator 6, rectified Hochspan ⁇ voltage U h v is then applied to the X-ray tube 5.
  • a scheme is usually carried out such that the U h v as actual ⁇ value to a regulator (not shown) is fed, is compared there with a predetermined by the operator of the x-ray device voltage setpoint and, accordingly, a correction value ⁇ 5 generates value applied to the high voltage at the X-ray tube is given, for example, as a control variable to the inverter circuit, so that there according to the frequency and thus ultimately the high voltage is changed in the desired manner.
  • the transformer must be selected so in its ratio u that at a the highest Shaped ⁇ -made tube voltage U h v is accomplished by the predetermined ultimately from the network intermediate circuit voltage U DC. If the equal ⁇ straightening and smoothing means 4 is formed as a doubler circuit, the necessary ratio u by the aforementioned equation (1) is given.
  • Equation (4) shows that at the maximum tube current of the inverter circuit 2, a very high current must be taken. In order to reduce the maximum Storm site, therefore, the transmission ratio ü must be reduced. This ge ⁇ lingt shown by the inventive arrangement as shown in FIG. 2
  • FIG. 2 shows a block diagram as described in FIG.
  • a high-voltage capacitor 7 is connected in parallel and in series with the primary winding of a resonant circuit capacitor 8.
  • the high-voltage capacitor 7 and the resonant circuit capacitor 8 form a series resonant circuit with the stray inductance of the transformer 3.
  • the capacity of the high voltage capacitor 7 is selected such that the re ⁇ sonanzfrequenz the oscillating rice for tube currents between 0.5 and 1 A is in the range 10 kHz to 500 kHz.
  • the parasitic capacitance of the transformer 3 can be increased by construction ⁇ market measures.
  • the tube voltage U hV may be higher than the secondary voltage of the transformer ⁇ Se. 3
  • This can now be used to achieve a higher tube voltage U h v at lower tube currents. This can be selected via a smaller ⁇ gear ratio ü of the transformer 3, where ⁇ significantly reduced by the current in the inverter circuit. 2
  • a ⁇ Ver doubling of the voltage can be achieved whereby the transla- subscription ratio u can be halved.
  • Figure 3 shows a block diagram of an alternative embodiment to Figure 2.
  • a resonant circuit is formed on the primary side of the transformer 3, which its resonant frequency for tube currents of between 0.5 A and 1 A in the range 10 kHz to 500 kHz.
  • a resonant circuit capacitor 8 is connected in parallel with the primary winding of the transformer 3. Zusharm ⁇ Lich is inserted a resonant circuit coil 9 in series with the primary winding and the resonant circuit capacitor. 8
  • This embodiment achieves the same effect according to the invention as the embodiment according to FIG. 2.
  • FIG. 4 shows, in the form of a diagram, the voltage overshoot caused by the resonant circuit according to the invention in the circuits according to FIGS. 2 and 3 as a function of the AC frequency f (in kHz) of the inverter for three different operating points (tube currents).
  • the size of the Röh ⁇ renstroms is conces- by the cathode X-ray tubes led heating power determined.
  • the ratio s of the tube voltage to the secondary voltage of the transformer is plotted in FIG.
  • the load characteristic A shows the voltage ratio s for a tube current of 0.5 A.
  • the resonant frequency of the resonant circuit damped by the tube resistance is about 35 kHz.
  • the voltage overshoot at the resonant frequency is more than twice.
  • the tube voltage along the load characteristic A can be set to the desired value. It is also possible to control the inverter with the resonance frequency and to realize the voltage regulation via a pulse width modulation or phase shift.
  • the load curve B in FIG. 4 shows the profile of the voltage ratio s for a tube current of 0.75 A and the load characteristic C the course for 1 A tube current.
  • Figure 5 shows another embodiment of a high voltage generator 6 ⁇ similar to the circuit arrangement in Figure 2, except that no primary side Schwingwankapa ⁇ capacity is available.
  • FIG. 6 shows a further exemplary embodiment of a high-voltage generator 6 similar to the circuit arrangement in FIG. 3, wherein the series connection of the primary-side coil and capacitor has been replaced by a parallel circuit of a resonant circuit capacitor 8 and a resonant circuit coil 9.
  • the invention is preferably used in X-ray generators and Rönt ⁇ gen painen. Reference sign list

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  • Engineering & Computer Science (AREA)
  • Power Engineering (AREA)
  • X-Ray Techniques (AREA)

Abstract

L'invention concerne un ensemble de circuit et un procédé associé pour générer une tension d'alimentation de tube à rayons X (Uhv). L'ensemble comprend un circuit d'entrée réseau (1) pour générer une tension de circuit intermédiaire (Udc), un circuit onduleur (2) pour convertir la tension de circuit intermédiaire (Udc) en une tension alternative à haute fréquence (Uac), et un générateur de haute tension (6) qui convertit la tension alternative à haute fréquence (Uac) en une haute tension (Uhv) pour le tube à rayons X (5). Le générateur de haute tension (6) comporte un transformateur (3) et un condensateur haute tension (7), câblé en parallèle avec l'enroulement secondaire du transformateur(3), qui forme avec l'inductance de l'enroulement secondaire un circuit résonant dont la fréquence de résonance se situe dans la plage de fréquences allant de 10 kHz à 500 kHz. L'avantage de l'invention est que la capacité parasite de l'enroulement du transformateur est le cas échéant augmentée par un condensateur supplémentaire de façon à pouvoir l'utiliser avec profit comme composant d'élévation de la tension d'une source de haute tension.
PCT/EP2012/053152 2011-03-11 2012-02-24 Ensemble de circuit avec onduleur pour alimenter en tension un tube à rayons x et procédé associé Ceased WO2012123232A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102011005446A DE102011005446A1 (de) 2011-03-11 2011-03-11 Schaltungsanordnung mit Wechselrichter zur Spannungsversorgung einer Röntgenröhre und zugehöriges Verfahren
DE102011005446.4 2011-03-11

Publications (1)

Publication Number Publication Date
WO2012123232A1 true WO2012123232A1 (fr) 2012-09-20

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PCT/EP2012/053152 Ceased WO2012123232A1 (fr) 2011-03-11 2012-02-24 Ensemble de circuit avec onduleur pour alimenter en tension un tube à rayons x et procédé associé

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DE (1) DE102011005446A1 (fr)
WO (1) WO2012123232A1 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106649935A (zh) * 2016-09-27 2017-05-10 华北电力大学 一种特高压变压器空载直流偏磁励磁电流实时计算方法

Families Citing this family (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102014202179A1 (de) 2014-02-06 2015-01-22 Siemens Aktiengesellschaft Hochspannungstransformatoranordnung mit hoher, einstellbarer Streuinduktivität, Wechselrichterschaltung mit einer Hochspannungstransformatoranordnung und Verwendung einer Hochspannungstransformatoranordnung
DE102014202531A1 (de) * 2014-02-12 2015-08-13 Siemens Aktiengesellschaft Hochspannungstransformatorvorrichtung mit einstellbarer Streuung, Wechselrichterschaltung mit einer Hochspannungstransformatorvorrichtung und Verwendung einer Hochspannungstransformatorvorrichtung
DE102014202954A1 (de) 2014-02-18 2015-08-20 Siemens Aktiengesellschaft Verfahren zum Betrieb eines Resonanzwandlers und Resonanzwandler
EP3497706B1 (fr) * 2016-11-08 2020-02-12 Koninklijke Philips N.V. Inducteur pour haute fréquence et applications de grande puissance

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5272612A (en) * 1989-06-30 1993-12-21 Kabushiki Kaisha Toshiba X-ray power supply utilizing A.C. frequency conversion to generate a high D.C. voltage
DE4412766C1 (de) * 1994-04-13 1995-04-20 Siemens Ag Hochfrequenz-Hochspannungsgenerator
US6072856A (en) * 1997-06-12 2000-06-06 U.S. Phillips Corporation Power supply unit including a pulse width modulated inverter, notably for an x-ray generator
JP2002065657A (ja) * 2000-09-05 2002-03-05 Hitachi Medical Corp Ｘ線ｃｔ装置
DE10227841A1 (de) 2002-06-21 2004-01-15 Siemens Ag Schaltungsanordnung zur Erzeugung einer Röntgenröhrenspannung

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DE3462739D1 (en) * 1983-05-16 1987-04-23 Gen Electric Load voltage control for resonant inverter circuits
FR2790150B1 (fr) * 1999-02-19 2001-06-08 Ge Medical Syst Sa Procede de regulation d'un generateur a double resonance
US6934165B2 (en) * 2003-02-04 2005-08-23 North Star Power Engineering, Inc. Loosely coupled parallel resonant converter
CN101167241B (zh) * 2005-04-26 2010-06-23 皇家飞利浦电子股份有限公司 具有零电流开关的谐振dc/dc变换器

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5272612A (en) * 1989-06-30 1993-12-21 Kabushiki Kaisha Toshiba X-ray power supply utilizing A.C. frequency conversion to generate a high D.C. voltage
DE4412766C1 (de) * 1994-04-13 1995-04-20 Siemens Ag Hochfrequenz-Hochspannungsgenerator
US6072856A (en) * 1997-06-12 2000-06-06 U.S. Phillips Corporation Power supply unit including a pulse width modulated inverter, notably for an x-ray generator
JP2002065657A (ja) * 2000-09-05 2002-03-05 Hitachi Medical Corp Ｘ線ｃｔ装置
DE10227841A1 (de) 2002-06-21 2004-01-15 Siemens Ag Schaltungsanordnung zur Erzeugung einer Röntgenröhrenspannung

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106649935A (zh) * 2016-09-27 2017-05-10 华北电力大学 一种特高压变压器空载直流偏磁励磁电流实时计算方法
CN106649935B (zh) * 2016-09-27 2020-01-24 华北电力大学 一种特高压变压器空载直流偏磁励磁电流实时计算方法

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