X-ray imaging system

Abstract: The invention relates to an X-ray imaging system, comprising an X-ray source (2) for emitting an X-ray beam, a power supply unit (14) which is connected to the X-ray source, an X-ray detector (8) for converting the X-ray beam into an optical image, a television pick-up device (10) for converting the optical image into a video signal, a detection device (12) which is connected to the television pick-up device and which serves to form a control signal from the video signal, an output of the detection device being connected to the power supply unit for adjustment thereof, and a display unit which is connected to the output of the television pick-up device via an amplifier (18). When the reciprocal of the signal generated by the detection device is used as the gain factor for the amplifier, a stable brightness is obtained on the television monitor without giving rise to a light flash when the X-ray source is switched on. As a result, the duration of exposure can be reduced during medical imaging so that the dose applied is less and motional unsharpness is reduced.

Description: The invention relates to an X-ray imaging system, comprising an X-ray source for emitting an X-ray beam, a power supply unit which is connected to the X-ray source, an X-ray detector for converting the X-ray beam into an optical image, a television pick-up device for converting the optical image into a video signal, a detection device for applying to the power supply unit a first control signal that is a function of the light intensity of the optical image , a display unit for displaying the video signal from the television pick-up device after amplification by an amplifier and means for supplying a second control signal to a set terminal of the amplifier for adjustment of a gain factor of the amplifier. An X-ray imaging device of this kind is known from US-A-4 910 592. This document describes an X-ray imaging system comprising two control loops. The first control loop is an automatic dose control loop which adjusts the dose generated by the X-ray source so that the mean light intensity of the optical image produced by the X-ray detector is constant. A signal that is a function of this mean light intensity is detected by a detection device and applied as a first control signal to the power supply unit of the X-ray source. Thus, for objects which differ as regards X-ray absorption there are obtained video signals which have the same mean value or peak value. The video signal is applied to a television monitor via an amplifier which forms part of the second control loop, being an automatic gain control loop. A control component which is included in the second control loop provides an external control signal for adjusting the gain of the amplifier. As a result of the use of an automatic gain control loop, the brightness of the image on the television monitor remains constant also if, in the case of very thick objects or objects exhibiting a high radiation absorption, the automatic dose control loop cannot increase the dose to such an extent that the mean light intensity on the entrance screen of the television pick-up device is sufficient. It is desirable that, when the dose increases upon activation of the X-ray source, the automatic gain control loop also increases the gain factor for the video signal applied to the television monitor, so that an image having the desired mean brightness appears on the television monitor already during the adjustment period of the automatic dose control loop. Because the X-ray dose and the gain factor for the video signal then increase simultaneously, the video signal, however, exhibits a peak which is perceived as a disturbing flash in the X-ray image. It is an object of the invention to provide an X-ray imaging system in which an X-ray image of good quality is quickly obtained during dynamic imaging. To achieve this, an X-ray imaging system according to the preamble of Claim 1 is characterized in that the detection device is adapted to supply the second control signal, for which purpose the detection device determines a mean or peak value of the video signal in a measurement field within the video image, the second control signal supplied by the detection device adjusting the gain factor of the amplifier such that the gain factor is held at a predetermined maximum value until the mean or peak value exceeds a predetermined threshold value, after which the gain factor is adjusted in order to maintain the mean level of the signal applied to the display unit constant. As a result of these measures, the video signal applied to the television monitor quickly reaches its desired mean value or peak value, substantially without said values exhibiting overshoot. Because the video signal applied to the television monitor quickly reaches the correct value, in an X-ray system in accordance with the invention the first usable X-ray images become available already 0.17 s after activation of the X-ray source. This compares favourably with another known X-ray system disclosed in US-A-4 101 776 in which for the same circumstances the automatic gain control loop requires 0.45 s for correct adjustment of the video signal applied to the television monitor. As a result, the radiation dose applied to the object is more efficiently used; this is a major advantage in medical diagnostics considering the possible detrimental effects of X-rays on living organisms. An embodiment of the X-ray system in accordance with the invention is characterized in that an output of the detection device on which the first control signal is supplied is connected to a divider for forming the gain factor on a divider output, which gain factor is proportional to the reciprocal of the first control signal applied to the divider, the divider output being connected to the set terminal of the amplifier for supplying the second control signal thereto. In the divider the video signal supplied by the television pick-up device, referred to hereinafter as the camera signal, is divided by a peek value or mean value determined in the detection device during a sampling period, for example during a frame period (40 ms) or a field period (20 ms). In static situations, where the mean light intensity on the entrance face of the television pick-up device is constant, a normalized video signal appears at the amplifier output. In dynamic situations, the mean values or peak values of the video signals generated by the television pick-up device during successive frame of field periods deviate from one another, so that a small deviation from the normalized video signal arises, which deviation depends on the difference in mean brightness or peak brightness between two successive frames or fields. A further embodiment of an X-ray imaging system in accordance with the invention is characterized in that the detection device comprises at least two detection modules, an input of each module being connected to the television pick-up device, the output of a first detection module being connected to the power supply unit, the output of a second detection module being connected to the set terminal of the amplifier. Because the automatic dose control and the gain factor for the video signal applied to the television monitor can be independently adjusted, an optimum image quality can be combined with an as low as possible dose, for example by peak value detection within a measurement field in the first detection module and by detection of the mean value within a second measurement field in the second detection module. Furthermore, the control behaviour of the automatic dose control loop can be adjusted by adaptation of the size and the location of the measurement field of the second detection module within the video image. Some embodiments of an X-ray imaging system in accordance with the invention will be described in detail hereinafter with reference to the accompanying drawing. Therein: Fig. 1 diagrammatically shows a known X-ray imaging system, Figs. 2a and 2b show the peak value of the video signal generated by the television pick-up device and the video signal applied to the television monitor for an increasing radiation dose in a known X-ray imaging system, Fig. 3 diagrammatically shows an X-ray imaging system in accordance with the invention, Fig. 4 shows the measure response of an X-ray imaging system in accordance with the invention to a linearly increasing radiation dose, Fig. 5 shows the peek value of the video signal applied to the television monitor in an X-ray imaging system in accordance with the invention for a video signal from the television pick-up device which increases in accordance with Fig. 2a, and Fig. 6 shows a block diagram of a detection device in accordance with the invention. Fig. 1 shows an X-ray imaging system which comprises an X-ray source 2 emitting an X-ray beam 4 which irradiates an object 6. An X-ray detector 8, preferably an X-ray image intensifier, converts the X-ray beam, locally intensity-modulated by the object 6, into an optical image which appears on an exit screen of the X-ray image intensifier. This optical image is converted into a video signal Vc by a television pick-up device, for example a video camera comprising a pick-up tube or a CCD sensor. This video signal is applied to a first detection device 12 which determines a mean value or a peak value of the video signal in a measurement field within the video image generated by the video camera 10. The first control signal formed in the detection device 12 is applied to a power supply unit 14 of the X-ray source 2. When the current through the filament of the X-ray source 2 is increased, the intensity of the X-rays increases; when the high voltage of the X-ray source is increased, the electrons are accelerated faster to the anode, so that the energy and hence the penetrating power of the X-rays increases. The mean light intensity on the entrance screen of the video camera 10 is kept constant by varying the current and the high voltage of the X-ray source 2 in dependence on the thickness of the object 6 to be irradiated, which variation is between, for example 0.1 mA and 1200 mA and between 40 kV and 125 kV, respectively. Because the dose control loop I, formed by the X-ray source 2, the video camera 10, the detection device 12 and the power supply unit 14, cannot increase the X-ray dose sufficiently to keep the mean light intensity on the entrance screen of the video camera 10 constant in the case of very thick or highly radiation-absorbing objects 6, a gain control loop II is required to keep the mean brightness level of the image displayed on the television monitor 16 constant. The video signal generated by the video camera 10 is amplified by an amplifier 18. The output signal Vm of the amplifier 18 is applied to a second detection device 20 which determines a mean value or a peak value in a measurement field within the video image. Via a differential amplifier 22, the signal originating from the detection device 20 is compared with a reference voltage Vref which corresponds to a desired mean brightness level of the video image. The difference voltage originating from the differential amplifier 22 is applied, via an integrator 21, as a second control signal to a set terminal 24 of the amplifier 18 so that the gain factor is adapted. Fig. 2a shows the variation of the video signal Vc generated by the video camera 10 when the X-ray source 2 of a Philips X-ray apparatus type BV 25 is switched on. Fig. 2b shows the variation of the video signal Vm applied to the television monitor 16 when use is made of the known gain control loop II. Because the average value of the video signal Vc applied to the amplifier 18 is lower than the reference voltage Vref, the gain factor of the amplifier 18 is increased. However, because the video signal Vc from the video camera 10 increases during the period of time required by the gain control loop II to increase the gain factor, an overshoot of 190 mV occurs in the video signal Vm applied to the television monitor. This overshoot could be prevented by incorporating a greater delay in the gain control loop II. However, this has the drawback that radiation which is strongly attenuated by the object 6 cannot be used for medical imaging. Making the gain control loop II faster would cause more overshoot and would not lead to an improvement either. The response as shown in Fig. 2b occurs in the case of critical damping of the gain control loop II and is optimum for such a control loop. Fig. 3 shows an X-ray imaging system in which the automatic gain control loop is replaced by a divider 19. The divider 19 forms the second control signal for adjusting the gain factor of the amplifier 18 by dividing the reference voltage Vref by the signal applied to the divider 19 by the detection device 12 and applies the second control signal to the set terminal 24 of the amplifier 18. During a field period a mean value or peek value of the video signal Vc is determined in the detection device 12. The video signal formed by the video camera 10 is divided by this value during the next field period. When the video signal from the video camera 10 increases, as shown in Fig. 2a, the peek values and/or the mean values of the video signal are small during the initial field periods of the video signal, so that the gain factor of the amplifier 19 becomes very high. In order to prevent this, the detection device 12 forms a predetermined threshold value on its output, for example for mean values or peak values below this threshold value. As soon as the output signal of the detection device 12 exceeds the threshold value, the mean level of the video signal Vm applied to the television monitor 16 is controlled to Vref. This is illustrated in Fig. 4. In Fig. 4 it is assumed that the mean level of the video signal Vc from the video camera 10 linearly increases as a function of time: Vc = t. In Fig. 4 the voltage is plotted as a function of time in arbitrary units. In the divider 19 the gain factor k(t) is formed by the quotient of the reference voltage Vref and the mean value or peak value measured during a preceding frame period T. In the case of uniform illumination of the entrance screen of the video camera 10, the brightness in any point of the video image is equal to the mean value and the peek value. In this case the gain factor k(t) is given by: k(t) = Vref/Vc(t-T). For a reference voltage Vref amounting to 10 V and a frame period T amounting to 1 s, k(t) is shown as a curve a in Fig. 4. For small values of t the gain factor k(t) tends to become infinite. If the threshold value of the detection device 12 is 5 V, the maximum gain factor in this case equals 2. For the time interval 0 < t < 6 s: Vm = 2Vc = 2t. After 6 seconds the gain factor k(t) decreases if Vref/(t-T) = 10/(t-1) as denoted by the non-interrupted part of the curve a in the Figure. For the signal Vm(t) applied to the television monitor 16 it then holds good that: Vm(t) = Vc(t).k(t) = 10t/(t-1). As is shown in Fig. 4, after 6 seconds Vm(t) follows the non-interrupted part of the curve b. Fig. 4 shows that the video signal Vm(t) exhibits an overshoot with respect to the reference voltage Vref which is greater as the maximum gain factor of the amplifier 18 is greater (the threshold value of the detection device is then lower). For a smaller maximum gain factor (less slope of Vm(t)) less overshoot occurs, but more time is required before Vm(t) is stabilized at the level of Vref. It can also be deduced from Fig. 4 that the overshoot can be reduced by way of a shorter integration time of the detection device. Fig. 5 shows the response of the X-ray imaging system in accordance with the invention to a video signal Vc which increases according to the curve shown in Fig. 2a. After 0.17 s, the level of the video signal has been stabilized at the level Vref which amounts to 300 mV in the present case. The overshoot, amounting to 30 mV, is so small that the light flash occuring on the monitor 16 when the known gain control loop is used is now absent. It has been found that when the video signal Vm applied to the television monitor is appropriately adjusted, the exposure duration can be reduced by 36% in the so-called snapshot mode. As a result, less motional unsharphess occur in the image and the dose applied to a patient is reduced. Fig. 6 diagrammatically shows the detection device 12. The detection device comprises three detection modules 30, 32 and 34, the detection module 32 being formed by a video mean value detector, the detection modules 30 and 34 being formed by video peak value detectors. The video signal Vc from the television camera 10 is applied to the detection modules 30, 32 and 34 after amplification by way of an amplifier 36 having a variable gain factor. Depending on the position of the switch 38, the signal Vs applied to the power supply unit is formed by a mean value or by a peak value. These values are determined within a measurement field of the video image, which measurement field can be adjusted via adjusting terminals 42 and 44. Depending on the position of the switch 40, the divider 19 receives a mean value or a peak value of the video signal Vc. The divider 19 forms the quotient of the gain factor of the amplifier 36 and the amplified video signal Vc, so that the reciprocal of the peak value or the mean value of the video signal Vc appears at the output of the divider 19. This value is applied to the amplifier 18 which is in this case formed by a multiplier, an input of which constitutes the amplifier set terminal 24. In the multiplier 18 the video signal Vc is divided by the mean value or the peak value, so that the video signal Vm applied to the television monitor 16 has a constant mean brightness level. The advantage of separate detection modules 30-34 resides in the fact that the control behaviour of the automatic dose control loop and the adjustment behaviour of the gain of the video signal Vm can be separately adapted, by selection of peak value detection or mean value detection within an adjustable measurement field, to the imaging method used, for example fluoroscopy or snapshots.

Claims: An X-ray imaging system, comprising an X-ray source (2) for emitting an X-ray beam (4), a power supply unit (14) which is connected to the X-ray source, an X-ray detector (8) for converting the X-ray beam into an optical image, a television pickup device (10) for converting the optical image into a video signal, a detection device (12) for applying to the power supply unit (14) a first control signal that is a function of the light intensity of the optical image, a display unit (16) for displaying the video signal from the television pick-up device (10) after amplification by an amplifier (18) and means for supplying a second control signal to a set terminal (24) of the amplifier for adjustment of a gain factor of the amplifier, characterized in that the detection device (12) is adapted to supply the second control signal, for which purpose the detection device determines a mean or peak value of the video signal in a measurement field within the video image, the second control signal supplied by the detection device adjusting the gain factor of the amplifier (18) such that the gain factor is held at a predetermined maximum value until the mean or peak value exceeds a predetermined threshold value, after which the gain factor is adjusted in order to maintain the mean level of the signal applied to the display unit (16) constant. An X-ray imaging system as claimed in Claim 1, characterized in that an output of the detection device (12) on which the first control signal is supplied is connected to a divider (19) for forming the gain factor on a divider output, which gain factor is proportional to the reciprocal of the first control signal applied to the divider, the divider output being connected to the set terminal (24) of the amplifier (18) for supplying the second control signal thereto. An X-ray imaging system as claimed in Claim 2, characterized in that the amplifier (18) comprises a multiplier, a first input terminal of which constitutes the set terminal (24), a second input terminal thereof being connected to the television pick-up device (10). An X-ray imaging system as claimed in Claim 1, 2 or 3, characterized in that the detection device (12) comprises at least two detection modules (30, 32, 34), an input of each module being connected to the television pick-up device (10), the output of a first detection module being connected to the power supply unit (14), the output of a second detection module being connected to the set terminal (24) of the amplifier (18).

Inventors: LOONEN ANTONIE ROCHUS MARIA, LOONEN, ANTONIE ROCHUS MARIA
Applicants: PHILIPS NV, N.V. PHILIPS' GLOEILAMPENFABRIEKEN
Application year: 1991
Main classification: H05G1
IPC codes: H05G1, A61B6, H04N5