EP4120801A1 - Imagerie par rayons x avec commutation kvp rapide - Google Patents

Imagerie par rayons x avec commutation kvp rapide Download PDF

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Publication number
EP4120801A1
EP4120801A1 EP21185350.2A EP21185350A EP4120801A1 EP 4120801 A1 EP4120801 A1 EP 4120801A1 EP 21185350 A EP21185350 A EP 21185350A EP 4120801 A1 EP4120801 A1 EP 4120801A1
Authority
EP
European Patent Office
Prior art keywords
voltage
capacitance
pull
push
buffer
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.)
Withdrawn
Application number
EP21185350.2A
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German (de)
English (en)
Inventor
Oliver Woywode
GLEICH Bernhard
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.)
Koninklijke Philips NV
Original Assignee
Koninklijke Philips NV
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Filing date
Publication date
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Priority to EP21185350.2A priority Critical patent/EP4120801A1/fr
Priority to PCT/EP2022/068688 priority patent/WO2023285226A1/fr
Publication of EP4120801A1 publication Critical patent/EP4120801A1/fr
Withdrawn legal-status Critical Current

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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
    • H05G1/10—Power supply arrangements for feeding the X-ray tube
    • 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
    • H05G1/22—Power supply arrangements for feeding the X-ray tube with single pulses

Definitions

  • the invention relates to X-ray imaging with fast kVp-switching.
  • the invention relates to a voltage generator for X-ray imaging with fast kVp-switching between at least a first voltage level and a second voltage level different to the first voltage level. Further, the invention relates to an X-ray imaging system, and a method of controlling X-ray imaging with fast kVp-switching.
  • So-called Fast kVp-switching is a dual energy acquisition technique in X-ray imaging, particularly in computed tomography (CT), in which technique alternating views correspond to the switched low and high tube voltages, i.e. utilizing scans at different voltage and/or energy levels, "low-kV” and "high-kV".
  • projections may be acquired at a first, high(er) voltage of about 120 to 150 kilovolts (kV) and or another suitable value or range, and at a second, low(er) voltage of e.g. 70 to 100 kV or another suitable value or range, e.g. switching between the different voltage levels at every few or fractions of milliseconds.
  • spectral imaging can be performed using fast kVp-switching.
  • a voltage generator for X-ray imaging with fast kVp-switching between at least a first voltage level and a second voltage level different to the first voltage level.
  • the voltage generator comprises a voltage input, and a voltage output.
  • the voltage generator comprises a voltage multiplier circuit, connected to the voltage input and to the voltage output, and comprising a network of a push-pull capacitance and at least one diode, and configured to provide, in response to a input voltage received via the voltage input, at least the first voltage level and the second voltage level at the voltage output in an alternating manner.
  • the voltage generator comprises a buffer capacitance arranged with respect to the voltage output. Thereby, a ratio of push-pull capacitance to buffer capacitance is between 0.5 and 3.
  • the voltage generator can provide a good compromise between ripple and speed. It is noted that a large value of buffer or smoothing capacitance typically decreases the ripple of the output voltage at the expense of longer transition times between the low and high kV level. Vice versa, small values of the buffer capacitance will yield speed but will introduce more ripple into the waveform which would degrade image quality if left uncorrected.
  • the above voltage generator allows the push-pull capacitance to be reduced in addition to a reduced buffer capacitance to decrease the ripple in the output voltage.
  • an electrical current provided to an X-ray tube connected to the voltage output has discharged the buffer capacitance only.
  • the voltage across the push-pull capacitance still corresponds to the high kV level because no charge was being removed.
  • the one or more high voltage diodes start conducting and a transient process occurs that eliminates this charge imbalance at the expense of a high voltage overshoot even if the generator injects energy only for a single half period of the resonant current. This can cause a large ripple in the output voltage and distorts the fidelity of the kVp-switching waveform. It has been found that a smaller value of the push-pull capacitance can reduce this effect in two ways. First, the voltage overshoot when the voltage generation is turned on, is smaller. Second, the smaller amount of charge can be removed faster during the transient.
  • the term "fast kVp-switching” means a dual energy acquisition technique in X-ray imaging, particularly in computed tomography (CT), in which technique the X-ray source voltage is switched between different voltage and/or energy levels, "low-kV” and "high-kV", between individual projections.
  • the X-ray source e.g. X-ray tube
  • a preferred application or use of the voltage generator is an X-ray imaging device or system for CT applications configured to provide fast kVp-switching, wherein "fast kVp-switching" may be understood as the tube voltage is changed between individual projections of the scanning procedure.
  • the smallest amount of ripple in the output voltage may be obtained if the push-pull capacitance equals exactly the buffer capacitance. However, it is not trivial to determine exactly this amount of capacitance. Therefore, it is not trivial neither to match exactly the push-pull capacitance to this residual buffer capacitance. Thus, a suitable range is therefore selected and the push-pull capacitance may be selected or chosen between approx. 50% up to approx. 300% of buffer capacitance, i.e. with a factor between approx. 0,5 to approx. 3 of buffer capacitance.
  • the push-pull capacitance is larger than 300% of the buffer capacitance the voltage peaks can become too large and if the push-pull capacitance is smaller than 50% of the buffer capacitance the power density of the voltage generation can become too low.
  • the voltage multiplier circuit may be broadly understood as an electrical circuit that is configured to convert electrical power, particularly AC electrical power, from a lower voltage to a higher DC voltage, typically using a network of one or more capacitors and one or more diodes.
  • the voltage multiplier circuit may be formed unipolar or bipolar.
  • the voltage multiplier circuit may comprise multiple high-voltage cascades, which may be formed as e.g. a Cockcroft-Walton generator, Villard multiplier circuit or Siemens circuit, or the like.
  • the buffer capacitance may also be referred to as a smoothing capacitance, since the buffer capacitance smooth the output voltage, thereby reducing ripple.
  • the buffer capacitance may be broadly understood as a total capacitance measured from the X-ray source position, e.g. X-ray tube position, where all diodes are in a non-conducting state.
  • the push-pull capacitance may be broadly understood as a series connection of all, i.e. one or more, capacitors arranged within or along a single leg of the voltage multiplier circuit, which leg is defined as the series connection of one or more push-pull capacitors needed for the push-pull action of the voltage multiplier circuit.
  • a voltage multiplier circuit may have a number of legs.
  • the voltage multiplier circuit may be configured with only one single leg or with two, three or more legs.
  • the push-pull capacitance means the series connection of all capacitors in one leg.
  • the output voltage may have a trapezoidal signal shape, at least approximately. It is noted that an ideal square signal is not possible in practice for physics reasons.
  • switching and/or changing the voltage between the first voltage level and the second voltage level may be in an order of at least 100 mega volts per second (MV/s), preferably of at least 300 MV/s, and most preferably of 1000 MV/s, or even more MV/s. In a respective embodiment, this may be understood as "fast kVp-switching".
  • the buffer capacitance may be below 1000 pikofarad (pF), preferably below 300 pF, further preferably below 150 pF, and most preferably below 50 pF.
  • pF pikofarad
  • the buffer capacitance, and in turn the push-pull capacitance are particularly small, thereby increasing the speed of switching while still reducing the ripple.
  • the push-pull capacitance may comprise a number of capacitors arranged in one or more high-voltage cascades.
  • the voltage multiplier circuit may comprise multiple high-voltage cascades, e.g. two, three, four, five, or more. In this way, the voltage generator may be provided to a wide range of applications.
  • the buffer capacitance may comprise a high voltage cable capacitance, wherein the high voltage cable is connectable or connected to the voltage output.
  • fast kVp-switching may further be improved in terms of speed by removing all dedicated buffer capacitors and rely only on some residual and/or parasitic, quasi unavoidable, buffer capacitance of the voltage generator and/or X-ray or CT imaging device or system.
  • This residual or unavoidable capacitance is inherent to the high voltage cable that connects to the X-ray tube of the X-ray or CT imaging device. In this way, the speed of kVp-switching may be increased, and the number of dedicated buffer capacitors may be reduced or their need may be eliminated or omitted at all.
  • the buffer capacitance may comprise a high voltage measurement divider capacitance, wherein the high voltage measurement divider is connectable or connected to the voltage output.
  • fast kVp-switching may further be improved in terms of speed by removing all dedicated buffer capacitors and rely only on some residual and/or parasitic, quasi unavoidable, buffer capacitance of the voltage generator and/or X-ray or CT imaging device or system.
  • This residual or unavoidable capacitance is inherent to the high voltage measurement divider that connects to the voltage output. In this way, the speed of kVp-switching may be increased, and the number of dedicated buffer capacitors may be reduced or their need may be eliminated or omitted at all.
  • the buffer capacitance may comprise at least one, preferably dedicated, capacitor.
  • one or more capacitors may be included in the voltage multiplier circuit. In this way, the buffer capacitance can be increased, for example, to obtain a more smooth output voltage.
  • the buffer capacitance is solely formed by one or more residual and/or parasitic capacitances.
  • the voltage multiplier circuit may omit a dedicated buffer capacitor etc., wherein the push-pull capacitance may be adjusted to the residual and/or parasitic capacitance(s).
  • the capacitance of a high-voltage cable of the X-ray imaging system may be determined by measurement, modelling, calculation based on a datasheet or the like, experience, etc., and the push-pull capacitance may be adjusted by selecting or choosing one or more suitable capacitors or the like. In this way, the buffer capacitance can be reduced to a minimum value, since the buffer capacitance utilized is inherent to the voltage generator and/or X-ray or CT imaging device or system.
  • the voltage multiplier circuit may comprise a number of high-voltage cascades comprising a number push-pull capacitors forming the push-pull capacitance, without a dedicated buffer capacitor. In this way, the speed of kVp-switching can be increased and at the same time the ratio of push-pull capacitance and buffer capacitance can be well adjusted.
  • the voltage multiplier circuit may comprise a unipolar or bipolar multi-stage high-voltage cascade. In this way, the voltage generator may be provided to a wide range of applications.
  • an X-ray imaging system that is configured for fast kVp-switching between at least a first voltage level and a second voltage level different to the first voltage level.
  • the X-ray imaging system comprises a voltage generator according to the first aspect, and an X-ray source, connected to a voltage output of the voltage generator to receive a voltage signal switching between the first voltage level and the second voltage level.
  • the X-ray imaging system may comprise a gantry, and the X-ray source may be arranged in the gantry. Further optionally, the X-ray imaging system may comprise a detector, and the X-ray source may be configured to project a beam of X-rays toward the detector on an opposite side of the gantry.
  • the X-ray imaging system may comprise a controller configured to control the voltage generator to change the X-ray source voltage utilizing the fast kVp-switching technique.
  • the X-ray imaging system may be a computed tomography system further comprising a controller configured to control the voltage generator to change the X-ray source voltage between individual projections.
  • a controller configured to control the voltage generator to change the X-ray source voltage between individual projections.
  • fast kVp-switching in CT can be used for e.g. spectral tomography.
  • the X-ray imaging system may be a CT scanner utilizing the fast kVp-switching technique.
  • the voltage generator may be configured to control switching between and/or changing the first voltage level and the second voltage level in an order of at least 100 MV/s, more preferably 300 MV/s, and most preferably 1000 MV/s.
  • fast kVp-switching may be understood as changing the X-ray source voltage, e.g. the tube voltage, between individual projections.
  • the X-ray source may comprise or be formed as an X-ray tube, which may be a vacuum tube configured to convert an electrical input power into X-rays.
  • the input signal may be provided by an AC voltage source, such as a transformer or the like, or any other suitable voltage generator.
  • the X-ray imaging system may comprise a high-voltage cable connecting a voltage output of the voltage generator and the X-ray source to each other.
  • the high-voltage cable inherently comprises a residual and/or parasitic, quasi unavoidable, buffer capacitance.
  • a buffer capacitance of the voltage generator and/or the X-ray imaging system comprises a high voltage cable capacitance, wherein the high voltage cable connects the voltage output of the voltage generator to the X-ray source.
  • a dedicated buffer capacitor can be omitted, still allowing reducing ripple in the output voltage.
  • the X-ray imaging system may comprise a high voltage measurement divider that is connectable or connected to the voltage output of the voltage generator.
  • the high voltage measurement divider inherently comprises a residual and/or parasitic, quasi unavoidable, buffer capacitance.
  • a buffer capacitance may comprise a high voltage measurement divider capacitance, wherein the high voltage measurement divider connects the voltage output of the voltage generator. In this way, a dedicated buffer capacitor can be omitted, still allowing reducing ripple in the output voltage.
  • a method of controlling X-ray imaging for fast kVp-switching between at least a first voltage level and a second voltage level different to the first voltage level comprises:
  • the method may be applied to the voltage generator of the first aspect and/or the X-ray imaging system of the second aspect.
  • the push-pull capacitance is selected to at least substantially match a residual and/or parasitic capacitance forming the buffer capacitance.
  • the buffer capacitance below 1000 pF, preferably below 300 pF, further preferably below 150 pF, and most preferably below 50 pF.
  • the buffer capacitance, and in turn the push-pull capacitance are particularly small, thereby increasing the speed of switching while still reducing the ripple.
  • the above embodiments may be combined with each other irrespective of the aspect involved. Accordingly, the method may be combined with structural features of the device and/or system of the other aspects and, likewise, the device and the system may be combined with features of each other, and may also be combined with features described above with regard to the method.
  • Fig. 1 shows an exemplary X-ray imaging system 1 that is configured for fast kVp-switching between at least a first voltage level and a second voltage level different to the first voltage level.
  • the X-ray imaging system is a computed tomography (CT) system in which the X-ray source voltage can be switched and/or changed between individual projections.
  • CT computed tomography
  • the X-ray imaging system comprises a voltage generator 100, an X-ray source 200, e.g. an X-ray tube, a gantry 300, a detector 400, a controller 500, and, optionally, a high voltage measurement divider 600.
  • the voltage generator 100 is configured to switch between the first voltage level and the second voltage level is in an order of at least 100 MV/s, more preferably 300 MV/s, and most preferably 1000 MV/s.
  • the X-ray source 200 is arranged in the gantry.
  • the X-ray source 200 is configured to project a beam of X-rays toward the detector 400 on an opposite side of the gantry 300.
  • the controller 500 is configured to control the voltage generator 100 to change the X-ray source voltage, i.e. the voltage provided by the voltage generator 100 to the X-ray source 200 utilizing the fast kVp-switching technique.
  • the voltage generator 100 and the X-ray source 200 are connected via a high-voltage cable, which is indicted in Fig. 1 by an arrow.
  • the optional high voltage measurement divider 600 may be arranged in a different way as illustrated in Fig. 1 , however, if applicable, both the high-voltage cable and the high voltage measurement divider 600 may contribute to a buffer capacitance with respect to the voltage generator 100 and/or the X-ray source 200.
  • FIG. 2 shows an exemplary voltage generator 100, which is configured for X-ray imaging with fast kVp-switching between at least a first voltage level and a second voltage level different to the first voltage level.
  • the voltage generator 100 comprises a voltage input 110, such as a transformer or the like, and a voltage output 120, which is connected to the X-ray source 200, e.g. via the high-voltage cable.
  • a voltage multiplier circuit 130 is connected to the voltage input 110 and to the voltage output 120, and configured to provide, in response to a input voltage received via the voltage input 110, at least the first voltage level and the second voltage level at the voltage output 120 in an alternating manner.
  • the voltage generator 100 and/or voltage multiplier circuit 130 may be bipolar, and may comprise or may be formed of a high-voltage cascade, wherein this exemplary embodiment comprises two cascade stages.
  • the multiplier circuit 130 comprises a network of a push-pull capacitance 131 and at least one diode 132, wherein in Fig.2 only an exemplary one of each is designated by the respective reference sign, for better illustration.
  • the push-pull capacitance 131 according to Fig.2 comprises push-pull capacitors C7 and C8. It is noted that the multiplier circuit 130 comprises a total of two legs, wherein a leg may be understood as the series connection of push-pull capacitors needed for the push-pull action of the voltage multiplier circuit 130. Further, the push-pull capacitance 131 may be understood as the series connection of all capacitors in one leg. Therefore, the push-pull capacitance 131 may also be referred to and/or considered as leg-wise push-pull capacitance 131.
  • the voltage generator 100 comprises a buffer capacitance 140, configured to smooth the output voltage and arranged with respect to the voltage output 120 and/or the X-ray source 200.
  • the buffer capacitance 140 is solely formed by the residual and/or parasitic capacitance of the high voltage cable connecting the voltage output 120 and the X-ray source 200.
  • a further, dedicated buffer capacitor can be omitted.
  • a ratio of push-pull capacitance to buffer capacitance is chosen to be between 0.5 and 3. It is noted that a value of the buffer capacitance 140 may be obtained by measurement, calculation, modelling, or the like, so that the push-pull capacitance 131 can be chosen in a suitable manner fulfilling the above ratio of 0.5 to 3. In other words, the push-pull capacitance 131 may be chosen between 50 % up to 300 % of the buffer capacitance 140.
  • the buffer capacitance is below 1000 pF, preferably below 300 pF, further preferably below 150 pF, and most preferably below 50 pF. It is noted that the buffer capacitance may be understood as the total capacitance measured from the x-ray tube position where all diodes are in a non-conducting state.
  • the push-pull capacitor C7 has a value of 0.5 until 3 times the value of parasitic high-voltage cable capacitance, which in Fig. 2 is designated by Cc.
  • the amount of charge stored in the push-pull capacitance 131 matches the charge stored in the buffer capacitance 140, e.g. the high voltage measurement divider and/or the charge stored in the capacitance of the high voltage cable, the deviation of the output voltage from an ideal trapezoidal shape is less severe.
  • Fig. 3 shows a further configuration of the voltage generator 100, which working principle is the same as described above, and which ratio of push-pull capacitance to buffer capacitance is also chosen to be between 0.5 and 3.
  • the voltage generator 100 according to Fig. 3 comprises or is formed as an unipolar three stage high-voltage cascade.
  • the voltage multiplier circuit 130 comprises push-pull capacitors C1, C4 and C7, and capacitors C2, C5 and C8 as push-pull capacitances 131, and dedicated buffer capacitors C3, C6 and C9 contributing to the buffer capacitance 140, which may further comprise the residual and/or parasitic capacitance of the high voltage cable.
  • the voltage multiplier circuit 130 comprises two legs, a leg defined as the series connection of push-pull capacitors needed for the push-pull action of the voltage multiplier circuit.
  • the push-pull capacitance 131 is the series connection of C1, C4, and C7 for one leg.
  • the push-pull capacitance 131 is the series connection of C2, C5, and C8.
  • the buffer capacitance 140 is formed of the parallel connection of Cc with the series connection of C3, C6, and C9.
  • the amount of charge stored in the push-pull capacitance 131 i.e. the push-pull capacitors C1, C4 and C7, and/or capacitors C2, C5 and C8 matches the charge stored in the residual buffer capacitance, i.e. the parallel connection of Cc with the series connection of C3, C6, and C9, the deviation of the output voltage from an ideal trapezoidal shape will be less severe.
  • the ripple in the output voltage across the load i.e. X-ray source 200, can be reduced even with a reduced value of push-pull capacitance 131.
  • Fig. 4 shows a further configuration of the voltage generator 100, which working principle is the same as described above, and which ratio of push-pull capacitance to buffer capacitance is also chosen to be between 0.5 and 3.
  • the voltage generator 100 according to Fig. 4 comprises or is formed as a bipolar high-voltage cascade.
  • the voltage multiplier circuit 130 according to Fig. 4 may be distinguished into two independent voltage multipliers connected differentially across the X-ray source 200, e.g. tube, and/or the voltage output 120.
  • each one of the two independent voltage multipliers has a single leg, one leg comprising the push-pull capacitor C1 as the push-pull capacitance 131, the other leg comprising the push-pull capacitor C2 as the push-pull capacitance 131.
  • two buffer capacitances 140A, 140B may be distinguished.
  • the first buffer capacitance 140A is made of the parallel connection of dedicated buffer capacitor C3 with the parasitic high-voltage cable capacitance, which in Fig. 4 is designated by CcAnode.
  • the second buffer capacitance 140B is made of the parallel connection of dedicated buffer capacitor C6 with parasitic cable capacitance, which in Fig. 4 is designated by CcCathode.
  • the push-pull capacitor C1 may be selected to have a value of 0.5 to 3 times the value of the first buffer capacitance 140A defined above.
  • the push-pull capacitor C2 may be selected to have a value of 0.5 to 3 times the value of the second buffer capacitance 140B.
  • Fig. 5 shows in a tube voltage / kV - time - diagram an exemplary output voltage waveform during kVp-switching.
  • the output voltage may be provided at the X-ray source 200, i.e. the tube.
  • the output voltage waveform could ideally have a rectangular shape as drawn with dashed line in the diagram, which in practice is physically approximated by a rather trapezoidal shape.
  • arrows A indicate a number of undesired voltage spikes appearing during kVp-switching, which may also be referred to as ripple, degrading image quality if left uncorrected.
  • the undesired spikes indicated in Fig. 5 by arrows A can be reduced by choosing an appropriate ratio of push-pull capacitance 131 to buffer capacitance 140, wherein the ratio is chosen to be between 0.5 and 3, i.e. the push-pull capacitance 131 has a value of 0.5 until 3 times the value of the buffer capacitance 140. It is noted that it has been found that reducing both the buffer capacitance 140 and also the push-pull capacitance 131 decreases the ripple in the output voltage with a good compromise between ripple and speed.
  • Fig. 6 shows in a flow chart a method of controlling X-ray imaging for fast kVp-switching according to an embodiment. The method may be carried out by the above X-ray imaging system 1 and/or the voltage generator 100.
  • step S1 the method comprises providing the voltage multiplier circuit 130, connected to the voltage input 130 and to the voltage output 120, and comprising the network of a push-pull capacitance 131 and at least one diode 132, and configured to provide, in response to a input voltage received via the voltage input 110, at least the first voltage level and the second voltage level at the voltage output 120 in an alternating manner.
  • the method comprises providing a buffer capacitance 140 with respect to the voltage output 140.
  • At least the push-pull capacitance 131 is selected to provide a ratio of push-pull capacitance to buffer capacitance between 0.5 and 3.
  • the method comprises controlling the voltage multiplier circuit 130 to generate an output voltage at the voltage output 120.

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  • X-Ray Techniques (AREA)
  • Apparatus For Radiation Diagnosis (AREA)
EP21185350.2A 2021-07-13 2021-07-13 Imagerie par rayons x avec commutation kvp rapide Withdrawn EP4120801A1 (fr)

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Application Number Priority Date Filing Date Title
EP21185350.2A EP4120801A1 (fr) 2021-07-13 2021-07-13 Imagerie par rayons x avec commutation kvp rapide
PCT/EP2022/068688 WO2023285226A1 (fr) 2021-07-13 2022-07-06 Imagerie radiographique à commutation kvp rapide

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Application Number Priority Date Filing Date Title
EP21185350.2A EP4120801A1 (fr) 2021-07-13 2021-07-13 Imagerie par rayons x avec commutation kvp rapide

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EP4120801A1 true EP4120801A1 (fr) 2023-01-18

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Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20170245356A1 (en) * 2014-09-26 2017-08-24 Nikon Metrology Nv High voltage generator

Patent Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20170245356A1 (en) * 2014-09-26 2017-08-24 Nikon Metrology Nv High voltage generator

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