CA1130464A - Power supply for triode x-ray tubes - Google Patents

Abstract

Abstract A power supply provides high voltage for a grid con-trolled x-ray tube. In the supply an oscillator generates a high frequency signal which is amplified and transformed to kilo-voltage. A voltage multiplier increases the kilovoltage to a potential suitable for the tube. The voltage multiplier in-cludes a bank of series capacitors which tends to maintain a constant high voltage when the tube is not conducting.

Description

11304~4 Background of the Invention This invention pertains to x-ray systems and more particularly concerns a high voltage power supply for grid controlled x-ray tubes.
X-ray tubes are thermionic emission devices and sensitive to both filament temperature and high voltage applied to the tube. Accordingly, most dental x-ray systems now in-clude some sort of feedback circuits to regulate high voltage and filament current.
A common way to provide high voltage is to apply line voltage to a high turns-ratio transformer, the output of which provides kilovoltage directly across the anode and cathode of the x-ray -tube. Because of the high turns ratio required by a direct conversion of the voltage, the high voltage transformers used in previous designs are quite large and bulky. Often there is high flux leakage in the transformer, resulting in a low coupling coefficient and a corresponding reduction of the efficiency of the transformer. Furthermore, because the sec-ondary coil requires many windings, -there is high internal re-sistance. Because of this high resistance, and also because of possible changes in leakage, the voltage across the tube is not constant but varies according to tube current, as well as line voltage.

jr/ ~ - 1 -1~304'~i4 Tube current, however, is highly sensitive to filament temperature and, therefore, accurate means of regulating filament current have been required, including means to pre-heat the filament before the high voltage is applied.
It will be seen that my invention offers substantial improvement over many pre-existing used circuits by meeting the objectives of reducing transformer size, cost and weight, providing an initially constant high voltage, providing compensation for line voltage fluctuations, and less sensitivity to tube current.
Broadly, the present invention may be seen as providing an x-ray power supply comprised of: an x-ray tube having a cathode, a grid, and an anode; an oscilla~or for generating a signal at a frequency substantially higher than line frequency; at least one linear amplifler connected to the oscillator to amplify the signal; a transformer having a primary and a secondary, the primary connected to the amplifier for transforming the amplified signal to a higher voltage across the secondary; a voltage multiplier, interposed between said secondary and the tube to provide a rectified voltage between the anode and the cathode at a multiple of the peak to peak voltage of the transformed amplified signal;
pulse means for applying a plurality of voltage pulses to the tube grid resulting in a plurality of current pulses through the tube and a corresponding plurality of x-ray emissions; and dosage means for turning off the voltage pulses to the grid and the corresponding x-ray emission when the desired x-ray dosage is reached.

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sd~ ~ -2-1~304~4 Brief Description of the Drawings Figure 1 is a schematic of the preferred embodiment of my invention;
Figure 2 shows voltage and currents found in the circuit of Figure l; and Figure 3 shows in detail some of the elements of Figure 1.

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~130464 _tailed Descrip-tion of the Invention An overview of a circuit embodying my invention is seen in Figure 1. While the invention will be described in connection with a preferred embodiment, it will be understood that it is not intended to limit the invention to that embodiment. On the contrary, it is intended to cover all alternatives, modifications, and equivalents as may be included within the spirit and scope of the invention as defined by the appended claims.
A triode x-ray tube 1 has a filament-cathode 2, a grid 3 and an anode 4. The cathode 2 is heated by a low voltage source 5. When a high voltage is applied across cathode 2 and anode 4, electrons are emitted from the hot cathode and strike the anode which emits x-rays. The high voltage is in kilovoltage and, in this example, is approximately 65 kilovolts DC. The filament voltage may be 4v DC. It is a known characteristic of grid-con-trolled tubes that high voltage may be maintained continuously between the cathode 2 and the anode 4, as the grid 3, which is interposed between cathode and anode will stop electron flow with a grid potential as low as about -200 volts DC.
In the preferred embodiment, an oscillator 6 generates a signal at a frequency many times above that of line frequency.
Preferably the oscillator frequency is 15-20 kilohertz compared to the typical line frequency of 50 or 60 hertz.
The output signal from the oscillator 6 is amplified by linear amplifiers, specifically, driver 7 and output stages 8 and 9. The amplified signal is applied across the primary of high voltage transformer 10 and transformed to a high voltage.
Following the preferred embodiment, the transformed voltage is then applied to voltage multiplier 11. The voltage ,, jr/ ~ - 3 -~13046~
multiplier 11 converts the transformed voltage to a higher, recitified positive voltage and applies it to the anode 4 of x-ray tube 1. The multiplier 11 includes a bank of series capacitors 12, 13, 14, 15, 16 which stores the high voltage until the tube is turned on. The voltage multiplier will be described in more detail later in this specification.
In accordance with the invention, tube 1 is pulsed by a grid control circuit 17 that periodically turns a negative grid voltage on and off for time periods, causing current pulses to flow through the tube during the off time as shown in Figure

2. The current pulse is on for a short duration (tl to t2), as for example 150 microseconds, so that the capacitors 12-16 only partially discharge, reducing the voltage across the tube by a value ~V. Sufficient off time (t2 to t3) is allowed between pulses to allow the capacitors to recharge. I have found that about 750 microseconds of off time is sufficient for recharging the capacitors. This means that in the example there is a 900 microsecond cycle (tl to t3).
In addition to the voltage variation, ~v, which is 2-0 due to the discharge of the capacitors, there may be a longer term high voltage variation due to changes in line voltage. In order to compensate for this line voltage variation, additional circuitry may be provided. As shown in Figure 1, a voltage divider 18 samples the voltage at the output of the voltage multi-plier 11. The sampled voltage is sent to a differential amplifier 19 where it is compared to a reference voltage 20. An error signal is provided by the amplifier which indicates if the volt-age appearing at the voltage multiplier is either too high or low.
In keeping with the invention, this error signal is directed to .~ , jr/~ - 4 -li30464 the frequency oscillator 6 and used to control the magnitude of the output signal, thereby completing a feedback loop so that the high voltage is maintained constant regardless of line fluctuations.
The use of a bank of multiple capacitors 12-16 in voltage multiplier 11 gives the desirable result of an initial high voltage that is independent of tube current or filament temperature. The discharge rate of the capacitors 12-16, is however, a function of tube current. It is, for the purpose of controlling tube current, still desirable to provide a regulated filament voltage source and to provide a pre-heat time period for the filament to reach temperature before the tube conducts. Never-theless the high voltage appearing across the x-ray tube will be more nearly constant and independent from filament temperature than many circuits known in the prior art.
The present invention is also concerned with x-ray ; dosage, which is a function of both the kilovoltage across the tube and the tube current integrated over time. A milliamp-second integrator 21 may be provided which turns the circuitry off when the current-time integral reaches a certain level. Several cur-rent integrating circuits are known, as for example, those dis-closed in U.S. Patent No. 4,039,811 and U.S. Patent No. 3,284,631.
Alternatively, as an additional feature of the invention, the number of grid pulses may be counted by pulse counter. Since the kilovoltage is fairly` constant and the filament is regulated, the tube current will be approximately constant. If the grid pulses are of uniform duration, the tube current over time pro-duct may be found by simply counting the pulses. When the number of pulses reach a predetermined quantity, the tube may be turned jr/~

off by means of the grid or by removing -the high voltage.
In the preferred construct:ion, the cathode is close to ground potential. Therefore, as an advantage of my invention, tube current may be measured merely by inserting an analog ammeter between the cathode and ground. The ammeter will read the average tube current. Since the tube is pulsed, the average current need only be multiplied by a constant to obtain the peak tube current, which may be used for adjusting the circuitry.
Figure 3 depicts some of the components of the circuit in further detail. Typical component values are given as examples only.
Oscillator 6 includes an operational amplifier having an RC feedback loop arrange to cause oscillation. An output signal from oscillator 6 has a frequency between 15-20 kilohertz which is directed to driver 7 which first amplifies the signal and then feeds it to a phase splitting transformer 24. Transformer 24 provides two signals of opposing phase which are then directed to the two push-pull power amplifiers 8, 9, which amplify the signals to sufficient power to drive the primary of the high voltage transformer 10 with 160 volts, peak to peak. The peak to peak secondary transformed voltage appearing across the sec-ondary is about 13KV and is connected to voltage multiplier 11.
The details of a high voltage transformer suitable for practicing the invention will now be given. The high voltage transformer consists of a primary winding of 80 turns of 22 gauge wire wound upon a core of high permeability material. Wound upon the primary winding is a secondary coil having twenty layers of 160 turns each of 40 gauge wire. The turns ratio is 80:1 com~ared to the 400:1 turns ratio of a conventional transformer. The jr/ ~

11304~4 primary winding may be center tapped, which allows B+ voltage to be delivered to the push-pull power amplifiers 8, 9. The core of the transformer should a high flux material, such as Stackpole 3C5. The geometry of the core is a rectangle of 3 by 2 3/4" outside dimensions having 5/8 inch square arms.
In the illustrated form, one advantage of the invention is that transformer size, and size, weight and cost are less with the present design.
We return to Figure 1 to study voltage multiplier 11, which is seen to have a plurality of stages. Each stage of the multiplier consists of two capacitors and two diodes arranged as shown in the drawing. I used 1200pf ceramic capacitors having a working voltage of 20 kilovolts.
The first stage includes capacitors 12 and 26 and diodes 31 and 32. Capacitor 26 and diode 31 DC restores the secondary voltage to a positive value above ground which is rectified to DC by diode 32 and capacitor 12. The process is repeated by succeeding stages. Five stages may be used to obtain an output of about 65 kilovolts. The components of the four remaining stages are capacitors 13-16, diodes 33-40 and capacitors 27-30.
The 65KV potential is retained by the bank of series capacitors 12, 13, 141 15, 16 until the tube 1 conducts, causing the capacitors to partially discharge.
Several additional advantages are offered by my in-vention over circuits commonly used in the past. For instance, the efficiency of the circuit is much greater, using only 195 watts compared to 1200 watts measured in a previous circuit.
Furthermore, it is known that when voltage is held in a bank of capacitors, an instantaneous power draw from line is not observed jr/~ 7 -as in some other units, resulting in less line swing. In some earlier units, impulse currents up to 1000 amperes were observed on the line when high voltage was turned on. Also, since the oscillator is running at a relatively high frequency and the grid control pulse is also relatively fas-t compared to a 50-60 hertz ; system, the error signal can be made more responsive thereby controlling the output kilovoltage much more accurately than is possible than with a 50 or 60 hertz system.
~ Thus, it is apparent that there has been provided, in 10 accordance with the invention, a power supply that fully satisfies the objectives and advantages set forth above. While the invention has been described in conjunction with a specific and preferred embodiment thereof, it is evident that many alternatives, modi-fications, and variations will be apparent to those skilled in the art in light of the foregoing description. Accordingly, it is intended to embrace all alterations, modifications and varia-tions as fall within the spirit and broad scope of the appended claims.

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Claims (3)

THE EMBODIMENTS OF THE INVENTION IN WHICH AN EXCLUSIVE
PROPERTY OR PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:

1. An x-ray power supply comprised of:
an x-ray tube having a cathode, a grid, and an anode;
an oscillator for generating a signal at a frequency substantially higher than line frequency;
at least one linear amplifier connected to said oscillator to amplify said signal;
a transformer having a primary and a secondary, the primary connected to said amplifier for transforming the amplified signal to a higher voltage across the secondary;
a voltage multiplier, interposed between said secondary and the tube to provide a rectified voltage between the anode and the cathode at a multiple of the peak to peak voltage of the transformed amplified signal;
pulse means for applying a plurality of voltage pulses to the tube grid resulting in a plurality of current pulses through the tube and a corresponding plurality of x-ray emissions; and dosage means for turning off the voltage pulses to the grid and the corresponding x-ray emission when the desired x-ray dosage is reached.

2. The x-ray power supply of claim 1 wherein the dosage means includes a milliamp-second current integrator which turns the voltage pulses off when the integral of the current pulses over time corresponds to the desired x-ray dosage.

3. The x-ray power supply of claim 1 where the dosage means includes a counter which counts the number of voltage pulses at the grid and turns the voltage pulses off when the number of voltage pulses reaches a value corresponding to the desired dosage.