Abstract:
The invention relates to the field of engineering physics in particular to the technique for detecting X-radiation, and it may be used for photometry, dosimetry as well as for measuring of space energy characteristics of optical-and-ionizing radiation fields with the aim of body X-ray scanning, human body in particular, to identify thereon or therein some highly undesirable objects or substances both for medical and security applications i.e. to prevent thefts and acts of terrorism and to provide the security of residential and other buildings that is in airports, banks and other high-risk areas. The X-ray screening of the body is realized by means of scanning it with a pre-shaped collimated bunch of X-radiation of low intensity due to moving the body and a source of X-radiation provided relative to one another, reception of X-radiation transmitted by the body, shaping and analysis of the image in its electronic form. It is the aim of the present invention to design a method and an apparatus which alongside with being safe and efficient make it possible to provide full body scanning with high precision. The aim set forth has been achieved by shaping the bunch of X-radiation as a single flat beam while X-radiation received at each scanning instant and converted into visible light radiation is in its turn converted into digital electronic signals. The radiation detectors filed are featuring a decreased noise level alongside with increased sensitivity and precision for registration of the intensity of X-radiation and also an extended dynamic range of X-radiation intensity values being registered which makes it possible to provide implementation of the method and the apparatus filed in the most advantageous way.

Description:
FIELD OF THE INVENTION 
     The invention relates to the field of engineering physics, in particular to the technique for detecting X-radiation and it may be used for photometry, dosimetry as well as for measuring of space energy characteristics of optical-and-ionizing radiation fields with the aim of body X-ray scanning, human body in particular, to identify thereon or therein some highly undesirable objects or substances both for medical and security applications i.e. to prevent thefts and acts of terrorism and to provide the security of residential and other buildings that is in airports, banks and other high-risk areas. 
     PRIOR ART 
     Nowadays problems of body X-ray scanning and of human bodies, in particular, to identify thereon or therein some highly undesirable objects or substances acquire special importance. This can be related for instance to the necessity of early diagnosis of various hard diseases such as tumours or tuberculosis. Security applications among many others may include theft prevention of drugs or precious stones and metals as well as provision of the security of air flights and that of banks, embassies, nuclear power centers and other high-risk areas. X-ray luggage examination (introspection) in airports is nowadays the most efficient way to provide the security of air flights. X-ray luggage examination systems (See the brochure of EUROPE SCAN COMPANY) are designed as a conveyer passing through a rectangular frame with an X-ray source being installed in the upper part of said frame and a receptor of X-radiation being installed in the lower part of the frame under the conveyer. The apparatus just described is not designed for scanning of the passengers due to high level irradiation of an X-ray source which is used to increase the resolution of the apparatus. 
     Scanning of passengers for the presence of metallic objects hidden under clothing is provided with the help of electromagnetic frames and metal detectors. An X-ray method hasn&#39;t been used for the examination due to its danger for health safety. 
     A number of efforts have been attempted lately to use low-dose X-ray scanning which could be applied for the examination of people without any threat for their health. 
     Known is a method and an apparatus for X-ray scanning (product name Body Search, see the brochure of American Science and Engineering). A person is scanned with a beam of X-radiation of sufficiently low intensity, while the radiation transmitted by the person&#39;s body is converted into an image which is used to judge on the presence of concealed objects. An apparatus for implementation of the method is comprised of a cabinet with an X-ray source of low intensity positioned therein, means for shaping an X-ray beam and a detector of X-radiation transmitted. Close to the cabinet there is located a movable carrier which is open on three sides. A person to be scanned is standing upright on the platform close to the cabinet with his/her face or back towards the latter. An X-ray source positioned at approximately half the person&#39;s height radiates a fanned divergent X-ray beam of low intensity which, when transmitted through the clothing, is reflected from the surface of the person&#39;s body. The X-radiation thus reflected is trapped by the detector to create thereon an image of the contents being available on the surface of the body, in the clothing or on the clothing of the portion of the body turned towards the cabinet. For full examination it is necessary to make scanning in two positions i.e. the face towards the cabinet and the back towards the latter. With this method the internal cavities of the body which at present are very often used for concealment of drugs and precious stones are not subjected to the examination. 
     Besides, the strongest radiation effects most sensitive of the human&#39;s organs which are located in the medium portion of the human&#39;s body, while the person&#39;s feet and especially shoes which also may be used for concealing the contraband appear to be out of view of the examiner. 
     Also known is a method and an apparatus for X-ray scanning of the body (U.S. Pat. No. 5,404,377, patented Apr. 4, 1995) by means of scanning the latter with a pre-shaped flat bunch of flat beams of X-radiation of low intensity by means of moving the body and an X-ray source relative to each other, reception of the X-radiation transmitted through the body, generating an optical image from this X-radiation, further transmitting and intensifying the optical image, generating an electronic image, and analysis of the latter. 
     In the apparatus described an X-ray source, a collimator of special design and a receptor made in the form of an array of the detectors of X-radiation are secured on a holder which moves relative to a stationary body. Each of the detectors of X-radiation contains the devices for generating an optical image from the X-radiation transmitted through the body, fibre-optic coupling elements, optic image magnifiers and means for converting an optical image to an electronic image. Visualization means include therein said receptor and means for processing said electronic image. 
     Since the transmission of information in the form of an optical image is usually accompanied by significant losses, the intermediate intensification of the image is required. To generate an image suitable for the conversion into an optical image a bunch (pile) of X-radiation beams is required, said beams having a definite height. A massive carrier with the devices supported thereon does not provide a sufficiently fast movement. Provision of a low dose received by the body on condition of a relatively low speed of movement of an X-ray source alongside with providing the intensity of X-radiation transmitted by the body sufficient to generate an optical image presents in itself rather a complicated problem. 
     Known is a radiation detector used for registration and photometry of optical radiation (Whitson G. 500 IC Implementation Circuits: Translated from English-M.: Mir, 1992, p. 278, p. 88). 
     A detector contains a photodiode connected in the plainest case either parallel to the load alpha in the series with the bias voltage source and with the load, while an ordinary input circuit of a current-or-charge amplifier is used as the load. 
     Known is a method and an apparatus for X-ray examination (U.S. Pat. No. 5,040,188, published Apr. 13, 1991) by means of X-raying said body with ah pre-shaped flat beam of X-radiation with the possibility of moving a source of X-radiation in relation to said body, reception of X-radiation transmitted through said body, generating an optical signal from said X-radiation, converting said optical signal into an electronic signal, providing analog-to-digital conversion, generating an electronic image and analysis of the latter. 
     A source of X-radiation, a special-design collimator and a receptor of X-radiation of the apparatus are rigidly secured on the holder. The holder may be moved in relation to the stationary body lying on a horizontal table and installed in the desired position. A receptor of X-radiation is made as an array of X-radiation detectors with each of said detectors containing a device for generating an optical image from X-radiation transmitted through the body and means for converting an optical image to an electronic one. 
     Visualization means include therein said receptor of X-radiation, an analog-to-digital converter and a device for processing said electronic image. 
     This technical solution does not provide for scanning the body on the whole but is designed for intense examination of its particular area. 
     Also known is a method and an apparatus for X-ray examination of the body (U.S. Pat. No. 5,850,836 published Dec. 22, 1998) by means of scanning it with a pre-shaped flat beam of X-radiation due to moving a source of X-radiation in relation to said body, reception of X-radiation transmitted through said body, conversion of said X-radiation into an electronic signal, providing analog-to-digital conversion, generating an electronic image and analysis of the latter. 
     A source of X-radiation, a special-design collimator and a receptor of X-radiation of the apparatus are rigidly secured on the holder which is moved in relation to the stationary body occupying a strictly specified position on a horizontal table. Visualization means include therein said receptor of X-radiation, an analog-to-digital converter and a device for processing said electronic image. According to one of the holder allocation embodiments a collimator and a receptor of X-radiation are positioned vertically and during scanning their movement along the body is provided due to the movement of the holder. 
     The speed of a massive holder with the devices fixed thereon cannot be sufficiently high. It is rather a complicated problem to preserve a minimum dose received by the body in combination with the power of X-radiation transmitted by the body, should a source of X-radiation move with a sufficiently low speed. 
     Known is a radiation detector used for registration and photometry of optical radiation (Whitson G. 500 IC Implementation Circuits: Translated from English-M.: Mir., 1992, p. 278, p. 88). 
     A detector contains a photodiode connected in the plainest case either parallel to the load or in the series with the bias voltage source and with the load, while an ordinary input circuit of a current-or-charge amplifier is used as the load. 
     Also known are one-dimensional or two-dimensional photodiode and phototransistor arrays (Zolotarev V. F. Nonvacuum Prototypes of CRTs:-M.: Energia, 1972, p. 216; Semiconductor Image Signal Formers: Edited by P. Jespers, F. Van de Ville and M. White; Translated from English-M.: Mir, 1979, p. 573) and also Image Receivers Employing Charge-Coupled Devices (CCD) (Charge-Coupled Devices: Translated from English/Edited by D. F. Barb.-M.: Mir, 1982, p. 240). These devices provide registration of optical energy characteristics in optical radiation fields. 
     Known are ionizing radiation detectors used for registration, dosimetry and spectrometry of nuclear radiation (Tsytovich A. P. Nuclear Electronics:-M.: Energoatomizdat, 1984, p.p. 5–33). The circuit diagram of these detectors is analogous to that of the detectors of optical radiation where photodiodes are replaced by ionization chambers, proportional counters, semiconductor sensors, scintillation counters or photodiodes which are used in combination with scintillators (Tsytovich). 
     Known are coordinate-sensitive detectors of ionizing radiation (IRCD) for one-dimensional and two-dimensional analysis used in nuclear experimental technique to registrate traces of elementary particles and to measure space distribution of nuclear particle flow (Zanevsky U. V. Wire Detectors of Elementory Particles:-M.: Atomizdat. 1978; Klenner P. Silicon Detectors. Nuclear Technique Abroad, 1986, N 6, p.p. 35–40). These detectors present either an array of wire electrodes positioned in a common gas volume or an array of strip electrodes produced by the surface evaporation on silicon crystal, said strip electrodes being coupled to an electronic readout device of coordinate information. 
     Out of a number of known radiation detectors the detector described by (Whitson, G.) appears to be most closely related to the one filed if the technical subject-matter is considered. This detector comprises a photodiode connected either in parallel to the load or in series with the load and a bias voltage source while an input circuit of a DC-or-charge amplifier serves as the load. This detector is designed for the registration of optical radiation, and when a photodiode is combined with a scintillator it also can be used for the registration of ionizing radiation. The disadvantage of such a detector is its low sensitivity which is caused to a considerable extent by noise and zero drift of DC amplifier used as the load of said detector. 
     SUMMARY OF THE INVENTION 
     The main aim targeted by the invention filed is implementation of a precision low-dose X-ray scanning. 
     It is the aim of the present invention to design a method and an apparatus which alongside with being safe and efficient make it possible to provide full body scanning with high precision. 
     There is one more accompanying aim to be solved which concerns elimination of the influence of the environmental changes in one of the apparatus modifications. 
     It is another aim of the invention to design an apparatus for converting visible light radiation into an electronic signal featuring a decreased noise level alongside with increased sensitivity and precision for registration of the intensity of X-radiation and also an extended dynamic range of X-radiation intensity values being registered which makes it possible to provide implementation of the method and the apparatus filed in the most advantageous way. 
     The aim set forth in a method of X-ray screening the body by means of scanning it with a pre-shaped collimated bunch of X-radiation of low intensity due to moving the body and a source of X-radiation relative to one another, reception of X-radiation transmitted by the body, shaping and analysis of the image in its electronic form has been achieved by shaping the bunch of X-radiation as a single flat beam while X-radiation received at each scanning instant and converted into visible light radiation is in its turn converted into digital electronic signals. 
     Preferably a flat beam of X-radiation is shaped as a vertical one. 
     In one of the embodiments of the method a flat X-ray beam is moved in a horizontal plane relative to the stationary body, and a receptor of X-radiation is moved in a horizontal plane synchronously with said beam. Movement of a flat beam of X-radiation is provided by means of a horizontal movement of a collimator with the speed ratio of the receptor and the collimator being constant. Movement of the collimator is provided with the help of a drive mechanism with a step motor, while movement of the receptor of X-radiation is also provided by means of a drive mechanism with a step motor, and it is synchronized with the collimator movement by maintaining the pre-defined ratio of their rotational speeds. 
     In another embodiment of the method a body is moved relative to a stationary source of X-radiation and a receptor of X-radiation. 
     A flat beam of X-radiation in this case is shaped with the scattering angle in the vertical plane of 37–43° and positioned such that the horizontal plane transversing the bottom portion of the body cuts off the beam by 2–5°. 
     In an apparatus for X-ray screening of the body comprising a carrier for positioning the body, a signal processing device, a source of X-radiation of low intensity and a holder with a collimator and receptor positioned thereon, said receptor being comprised of the detectors of X-radiation, each containing first device for conversion of X-radiation transmitted by the body into visible light radiation and second device for conversion of visible light radiation into an electronic signal, the aim set forth is achieved by the receptor made in the form of a vertical array of radiation detectors, with each detector containing said second device provided with a digital output and closely adjoining said first device. 
     The collimator made in the form of at least one pair of parallel plates and the detector are positioned vertically. 
     Preferably the holder is positioned horizontally with the possibility of movement in the vertical plane parallel to itself in relation to a stationary carrier for supporting the body. The holder contains thereon the horizontal guides for movement there along of the receptor provided with the drive mechanism with the step motor. The holder also contains thereon the horizontal guides for movement there along of the collimator also provided with the drive mechanism with the step motor. Said drive mechanisms are connected to the control unit for keeping of the pre-defined ratio of the rotation speeds of said step motors. The source of X-radiation is secured with the possibility of rotation around the vertical axis, and it is connected by a telescopic bar to the collimator. 
     In an alternative embodiment of the apparatus the holder is made n-shaped and positioned vertically, while one of the holder racks contains a linear receptor secured thereon and the second rack contains a collimator. 
     The carrier for positioning the body is made with the possibility of movement between the racks of the holder transversely to its surface, and it is provided with a separate motor and the guides, while the carrier on the whole is provided with a safeguard. 
     The source of X-radiation is positioned on the outer side of said second rack 20–50% higher than the level of the carrier. The collimator is secured inside said second rack of the holder. The space between the source of X-radiation and the second rack is covered with an additional housing made in the form of a pyramid with the base of the pyramid closely adjoining said rack and the corner at the top equal to the largest scattering angle of the beam of X-rays, while the additional housing contains positioned vertically therein at least one additional collimator made in the form of at least one pair of parallel plates. 
     The receptor may be comprised of at least two parts with the upper one making up 60–70% of the total height of the receptor and positioned at the angle of 4–6° in relation to the vertical plane towards the carrier for positioning the body. 
     To eliminate the influence of environmental changes the upper bar between the vertical racks is made as the four rods passing through the respective corner holes of the four flat rectangular plates positioned pairwise approximately at one third of the rods length at each of their ends at equal distances from the rod end with the ends of the rods being used for securing to the vertical racks. 
     In the first embodiment of a radiation detector filed containing a sensitive element e.g. a photodiode and a load connected in series, the improvement of precision and sensitivity at measuring the intensity of radiation is provided by means of an extra use within the detector structure of a key transistor and an interrogation pulse generator with respective coupling of these components to the other detector components. As a result a photocurrent of the photodiode is converted from a constant current to a pulsed one, this making it possible to measure the lower values of the latter with higher precision owing to the fact that the amplifiers of current and charge are lacking low-frequency noise components such as flicker noise and zero drift which are so much characteristic of DC current amplifiers. 
     Connection parallel to the load of N groups of components, said groups being comprised of the transistor and the photodiode which are coupled to N outputs of the interrogation pulse generator, provides a new feature of the radiation detector i.e. the ability to analyze the space distribution of the intensity of radiation being registered. In comparison to the prior art one-dimensional photodiode arrays [3] the embodiment filed makes it possible to implement a more extended dynamic range of the intensity of the radiation being registered. 
     This results from the fact that the dynamic range determined as the ratio of the maximum intensity of the radiation being registered to the minimum one is pre-defined by the variation range of an electric charge which has been integrated by the photodiode capacitance as well as the variation range of the integration period of said charge. The variation range of the charge integrated by the photodiode capacitance is determined as the ratio of the maximum value of the charge which has been integrated to the noise charge of the amplifier used to register said charge. All the other conditions being equal, the variation range of the charge which has been integrated by the photodiode capacitance is directly proportional to the square root of said photodiode capacitance value since the maximum value of the charge which has been integrated by the photodiode increases in direct proportion to the value of its capacitance, while the value of the amplifier noise charge increases in direct proportion only to the square root of the capacitance value at its input [5]. The variation range of the photocurrent integration period, with said integration provided by the photodiode capacitance, is in its turn defined by the ratio of its maximum possible value to the minimum one. The maximum duration of the photocurrent integration period is defined by the leakage resistance of the photodiode and that of the transistor as well as by the isolation of the circuit board, and it increases in direct proportion to the increase of the total capacitance of the photodiode and the key transistor. The minimum duration of the photocurrent integration period is defined by the time constant of the total capacitance charge of the photodiode and that of the key transistor during the generation of an integrated charge read-out signal. The duration of this time constant is directly proportional to the total capacitance of the photodiode and that of the key transistor as well as to the resistance of the open key transistor. Thus, the dynamic range of the intensities of the radiation being registered appears to be the wider the larger the capacitance of the photodiode and the charge leakage resistance therefrom are as well as the lower the resistance of the open key transistor is. A peculiar feature of the design filed is that both field-effect transistors (as in known photodiode arrays) and bipolar transistors may be used as a key transistor of the detector. The possibility of using bipolar transistors as the key transistor of the detector filed, said bipolar transistors having a hundred times steeper slope of characteristic as compared to field-effect transistors, makes it possible to decrease the resistance, of the open key transistor by hundred times and respectively, at all the other conditions being equal to extend the dynamic range of the intensities of the radiation being registered by hundred times. To provide a pre-defined dynamic range of the intensities of the radiation being registered the capacitors with required capacitance are connected in parallel to the photodiodes. To decrease the amplifier noise the detector may comprise L loads. 
     In the second embodiment of the radiation detector filed containing a radiation sensitive element and a load the increase of sensitivity and precision at registration of the radiation intensity is also provided by means of an extra use within the detector structure of a transistor and an interrogation pulse generator with respective coupling of these components to the other detector components. Interconnection between a supply voltage busbar of N groups of components, said groups being comprised of a key transistor, a radiation sensitive element and a capacitor, all being connected to N outputs of the interrogation pulse generator, provides a new feature of the radiation detector i.e. the ability to analyze the space distribution of the intensity of the radiation being registered. In comparison to the prior art one-dimensional photodiode arrays the second embodiment of the detector filed (as well as the first one) makes it possible to implement a more extended dynamic range of the radiation intensities being registered, and it also provides the possibility of using the radiation sensitive elements demanding a high-tension power supply voltage for their operation, e.g. such as proportional counters, ionisation chambers, photoresistors etc., extending the area of the possible detector applications. The increase of sensitivity and precision during registration of the radiation as well as the extension of the dynamic range of the radiation being registered is achieved in the second embodiment of the invention filed by the technical solution employed in the first embodiment of the invention filed which has been conditioned by a number of reasons making it possible to achieve the same results. To decrease the amplifier noise the detector may contain L loads. 
     In the third embodiment of the radiation detector filed containing an radiation sensitive element and a load the increase of sensitivity and precision during registration of the intensity of radiation is also provided by means of an extra use within the detector structure of a key transistor and an interrogation pulse generator with respective coupling of these components to the other detector components. The increase of sensitivity and precision during registration of radiation is achieved in the invention filed by the technical solution employed in the first embodiment of the invention filed which has been conditioned by a number of reasons making it possible to achieve the same results. A capacitor of the appropriate capacitance is connected between the first electrode of the key transistor and a common bus to provide the required dynamic range of the intensities of the radiation being registered. 
     The examples of the invention implementation are illustrated by the drawings that follow wherein: 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG. 1  is an overall view of the invention according to one of the preferred embodiments; 
         FIG. 2  illustrates an operational scheme of an apparatus in FIG.  1 .; 
         FIG. 3  shows the geometrical concept of a driving system; 
         FIG. 4  is an overall view of the invention according to another preferred embodiment; 
         FIG. 5  illustrates an operational concept of an apparatus in  FIG. 4  in the schematic form; 
         FIG. 6  shows the structure of a crossbar of an apparatus in  FIG. 4 ; 
         FIG. 7  illustrates movement through an apparatus in  FIG. 4  in the schematic form; 
         FIG. 8 ,  9 ,  10  illustrate the three modifications of a basic circuit of the first embodiment of the radiation detector filed which employs photodiodes as sensitive elements; 
         FIGS. 11 ,  12 ,  13  and  14  illustrate the four modifications of a basic circuit of the second embodiment of the radiation detector filed which employs various types of sensitive elements operating in the presence of a bias voltage including a high-tension voltage; 
         FIGS. 15 and 16  show the two modifications of a basic circuit of the third embodiment of the radiation detector filed using various types of sensitive elements operating in the presence of a bias voltage. 
     
    
    
     DETAILED DESCRIPTION OF THE INVENTION 
     The present invention may find a great number of various applications, and it will be illustrated by way of the two of them as examples i.e. medical application illustrated by an apparatus in  FIGS. 1–3  and nonmedical application illustrated by an apparatus in  FIGS. 4–7 . 
     A medical apparatus according to the invention shown in  FIG. 1  comprises a holder  1  with a collimator  2  and a receptor  3  positioned thereon, a source  4  of X-radiation of low intensity, a carrier  5  for positioning a body  6 , and a signal processing device  7  (see  FIG. 2 ). The receptor  3  is made in the form of a vertical array of the detectors  8  of X-radiation, each containing a device  9  for converting visible light radiation into a digital electronic signal, said device closely adjoining a device  10  for converting X-radiation transmitted by the body into visible light radiation which may possibly be of scintillation type. 
     The collimator  2  made in the form of at least one pair of parallel plates and the receptor  3  are positioned vertically. 
     The signal processing device  7  (see  FIG. 2 ) contains an interface unit  12  and a device  13  for processing the information thus received, said device possibly having the form of a computer—controlled operator&#39;s working station. An interface unit  12  is designed for control of all the apparatus units, check of their operations, conversion, and primary information processing. It is also used to provide the communication with the device  13  for information processing as well as to ensure the possibility of making the device  13  substantially distant from the source  4  of X-radiation with the aim of lowering the dosage of the service personnel. 
     In this apparatus a holder  1  is horizontally installed on a support  14  with the possibility of movement in the vertical plane parallel to itself in relation to a fixedly secured carrier  5  for positioning a body  6 , possibly a patient. The holder  1  contains thereon horizontal guides  15  for movement there along of a receptor  3  by a drive mechanism provided with the step motor  16  and horizontal guides  17  for movement there along of a collimator  2  by a drive mechanism provided with the step motor  18 . A source  4  of X-radiation as it is shown in  FIG. 3  is installed on a hinge  19  with the possibility of rotating round the vertical axis, and it is coupled by a telescopic bar  20  with the collimator  2 . 
     The above apparatus is provided with the control unit  21  for keeping of the pre-defined ratio of the rotation speeds of said step motors and the power supply unit  22  with connections (not shown) for applying the necessary voltages to the apparatus units. 
     A method filed has been implemented in the apparatus described in the following way. 
     The body  6  being scanned, possibly the human&#39;s body, referred to for the case described as “a patient” is positioned on the carrier  5 . The holder  1  is being moved in the vertical plane to achieve the appropriate positioning of the collimator  2  and the receptor  3  in relation to portion of the patient&#39;s  6  body being screened dependent on the height of the latter. The collimator  2  and the receptor  3  are positioned with high precision such that this flat vertical beam of X-radiation always impinges the vertical array of the X-radiation detectors  8  which the receptor  3  is comprised of. After turning on of the step motors  16  and  18  the synchronous movement of the collimator  2  and that of the receptor  3  is started along the respective horizontal guides  15  and  16 . The source  4  of X-radiation emits a bunch of beams which are shaped into one flat vertical beam by the collimator  2  with the help of two vertical plates  11 . The movement of the collimator  2  and that of the receptor  3  is synchronized such that a flat beam always impinges the receptor  3 . 
       FIG. 3  illustrates the synchronization concept of the driving system. During scanning the receptor  3  and respectively its detectors  8  of X-radiation are moving with the constant speed from point A to point B. The collimator  2  is being moved synchronously with the movement of said receptor but from point E to point F in such a way that the shadow projection of the slot of the collimator  2  of the flow of X-radiation emitted from point O always impinges the detectors  8 . 
     The source  4  of X-radiation is positioned in point O. The direction of its maximum radiation which is synchronous with the scanning of the receptor  3  and the slot of the collimator  2  is changed in such a way that it is always to be located at the OC line. 
     Since the movement of the collimator  3  is always effected with the constant speed along the chord of the circumference with the center in point O, the rotational angular speed of the source  4  in point O will be changeable. The synchronous operation of the movement system is provided due to he fact that simultaneously with the movement of the collimator  2  the telescopic bar  20  of the source  4  which is rigidly connected to the collimator  2  is being rotated around the point O with the center of X-radiation being located therein too. 
     It evidently follows from the similarity concept that to achieve constant projection of the collimator  2  on the detectors  8  within the whole of the scanning range it is just sufficient to provide movement in time of both components according to one and the same law. This design concept makes it possible to provide implementation of the movement system with relatively comprehensive means since for synchronous movement it is just sufficient to provide movement of the collimator  2  and that of the receptor  3  with constant speeds. 
     The synchronous movement of the collimator  2  and that of the receptor  3  in this case may be achieved only if the ratio of their speeds is maintained with high precision. Since the rotational speed of the step motors is eventually defined by the commutation frequency of their windings the aim of the synchronous movement is confined to synthesizing of the two frequencies with the strictly defined ratio, while it is necessary to have the possibility of changing this ratio with very small increments. Besides, to increase the movement smoothness of the collimator  2  and that of the receptor  3  as well as to improve the synchronization of their operation the steps of the motors have been divided by 8 times, this causing the respective increase of the commutation frequency of the motors also by 8 times. 
     Taking into account that for example the angular rotational speeds of the collimator  2  and the receptor  3  make up respectively 10 and 2 rotations per second, the number of steps per rotation is equal to 200 and the division factor is equal to 8, the computational frequencies for controlling the motors will be respectively equal to 16000 Hz and 3200 Hz i.e. the step motors  16  and  18  make up respectively 12800 and 3200 of divided steps per second, while with scanning time of 4 sec. the collimator  2  and the receptor  3  make up respectively 6400 and 12800 of steps. It can be easily calculated that the step value of the receptor  3  with the number of steps being equal to 12800 and the duty cycle of 600 mm is equal to approximately 50 μm that is to provide the required synchronism of the duty cycle with the precision of 50 μm it is necessary to maintain the number of steps during the scanning period with the precision of one step and this in its turn means that the frequencies are to be maintained with the precision of not worse than 1/12800. The possibility also must be provided to change the frequencies for the required sampling of their ratio with the same increments (1/12800). 
     It appeared feasible to solve this problem with relatively comprehensive hardware means due to the fact that the two controlling frequencies greatly differ from one another (approximately in five times). This made it possible to design an electronic synchronization circuit in the following way. The unit  21  using an appropriate programmer provides synthesizing of the reference rotational frequency of the collimator motor  18  (higher frequency) which is equal to approximately 2000 Hz. The sampling precision of this frequency is not so much critical as it is related only to the scanning period, but not to the consistency of the movement. Each pulse of the reference frequency is sequentially interrogated in the memory array with the lower scanning frequency of the receptor  3  having been pre-recorded therein. The volume of this memory array makes up 65536 Byte i.e. it slightly exceeds the number of steps of the collimator  2 . Consequently the position throughout the whole of the scanning area can be calculated and recorded in the memory with the precision of one step. The array to be stored is calculated on the grounds of the data received at the stage of system adjustment and alignment. The array stored is individual for each device. It is automatically loaded into the memory of the unit  21  without the operator&#39;s help just after the apparatus is turned on. 
     The duty cycle of the receptor  3  i.e. the distance between point A and B makes up 600 mm. The duty cycle of the collimator  2  i.e. the distance between points E and F makes up 150 mm. The distance H along the central axis OO′ between the center of rotation O and the movement plane of the receptor  3  makes up 1600 mm. The distance h between the center of rotation and the movement plane of the collimator  2  makes up 400 mm. The distance h′ between the center of rotation and the patient&#39;s location plane (designated by hatched line) depends on the dimension measurement of the patient and makes up within 800–900 mm i.e. it departs from the movement plane of the collimator  2  by 400–500 mm. The object geometrical increase factor (scaling factor) K which means the dimension ratio of the patient&#39;s shadow projection on the movement plane of the receptor  3  to the real dimensions of the patient will be equal to:
 
K=H/h′=2
 
     The patient&#39;s scanning time T during which the receptor  3  moves from point A to point B may have the four fixed values: 2, 4, 8 and 16 sec. The basic operation mode corresponds to the scanning time of 4 sec. with the movement speed V of the receptor  3  during this time being equal to:
 
 V=AB/T= 600/4=150  mm/sec.  
 
     And the movement speed V of the collimator  2  being equal to
 
 V=EF/T= 150/4=37.5  mm/sec.  
 
     In this operation mode (during scanning time of 4 sec.) the receptor  3  is being interrogated within t=10 msec.(0.01 sec.). Within this time the receptor  3  will move to the distances equal to
 
 S=V×t= 150×0.01=1.5  mm  
 
     Evidently this value (1.5 mm) will correspond to the spatial resolution of the patient&#39;s image being detected in the receptor&#39;s plane along the horizontal axis. Taking into account the geometrical increase the spatial resolution S in the object&#39;s plane will make up
 
 S=S/K= 1.5/2=0.75  mm  
 
     Consequently the movement values and the geometry of the system movement provide the spatial resolution of the object&#39;s image along the horizontal axis of 0.75 mm. The variation of the spatial resolution at variation of the scanning speed has directly proportional dependence i.e. when the speed is decreased, the spatial resolution is improved. 
     The receptor  3  may also be built as two vertical arrays of detectors  8  of X-radiation displaced by half the pitch in relation to positioning of detectors  8 . These arrays may be interrogated either in sequential or in parallel mode during scanning. The positioning pitch of the detectors  8  makes up 1.55 mm. The vertical spatial resolution on the receptor surface for the case described will be twice as small as the positioning pitch of the detectors  8 , thus making up approximately 0.8 mm. Taking into account a twofold geometric enlargement of the object (the object geometrical increase factor K=2) the vertical spatial resolution on the patient&#39;s location plane will be make up 0.4 mm. 
     A beam of X-radiation being transmitted by the patient&#39;s  6  body at each given scanning instant impinges the device  9  which may be for instance of scintillation type, and it is converted into visible light. This light being trapped by the devices  10  closely adjoining the devices  9  is further converted into digital electronic signals. The interrogation of the receptor  3  as it has been indicated is made within 10 msec. The output digital electronic signals are fed via the interface unit  12  to the device  13  for information processing. The dose received by the patient during one shot makes up from 0,3 to 0,9 mRem. 
     The movement of the collimator  2  and that of the receptor  3  both being light-weighted may be provided without practically any inertia with a wide range of speed adjustments. Direct conversion of visible light signals into digital electronic signals eliminates the losses and makes it possible to provide an efficient examination by especially low doses of X-radiation. 
     In an alternative embodiment of an implementation example of an apparatus for nonmedical application illustrated in  FIGS. 4–7  the components identical with those of the medical embodiment are shown by the same reference numerals. 
     In this embodiment a holder  1  is made n-shaped and positioned vertically with a linear receptor  3  secured to the first rack  23  of the holder  1  and a collimator  2  secured to the second rack  24 . A carrier  5  for positioning the body has been made with the possibility of movement between the rack  23  and  24  of the holder  1  transversely to the holder plane, and it is provided with a separate motor and the guides (not shown). 
     A source  4  of X-radiation is positioned on the outer side of said second rack  24  by 20–5.0% higher than the carrier  5  level (it is better shown at the  FIG. 5 ). The collimator  2  is secured inside said second rack  24  of the holder. The space between the source  4  of X-radiation and the second rack  24  is covered with an additional housing  25  in the form of a pyramid with the base of said pyramid adjoining said rack  24  and the corner at the top being equal to the largest beam scattering angle. As it is shown in  FIG. 5  this corner makes up about 43°. 
     Inside the additional housing  25  there is positioned vertically at least one additional collimator  26  made in the form of at least one pair of parallel plates. 
     The receptor  3  as it is shown in  FIG. 5  may be comprised of two parts with the upper one making up 60–70% of the total height of the receptor and positioned at the angle of 4–6° in relation to the vertical plane towards the carrier  5 . 
     The structure of the upper bar between the racks  23  and  24  is presented in  FIG. 6 . It is comprised of the four rods  27  passing through the respective corner holes  28  of the four flat rectangular plates  29 . The plates  29  are positioned pairwise at approximately one third of the length of the rods  27  from each of their corners at equal distances from the rod end and pairwise in-between. The ends of the rods  27  are used for securing to the vertical racks  23  and  24  by the usual-type fixation means(not shown). 
     The carrier  5  for positioning the body  6  is provided with a safeguard  30 . 
     The apparatus also contains the signal processing device  7  which contains an interface unit  12  and a device  13  for processing the information thus received, said device possibly having the form of a computer—controlled operator&#39;s working station. There is the power supply unit (not shown) for applying the necessary voltages to the apparatus units. 
     A method filed has been implemented in the apparatus described in the following way. 
     A flat vertical beam of X-radiation is generated from X-radiation emitted by the source  4  first with the help of at least one additional collimator  26  which is positioned vertically inside the additional housing  25 . This housing protects the beam from its accidental crossing by any object or body. Then the flat vertical shape of the beam receives an extra shaping with the help of the basic collimator  2  secured in the rack  23  of the holder  1 . The resulting beam of X-radiation is shaped with a scattering angle in the vertical plane of 37–43°. The collimator  2  and the receptor  3  are respectively positioned in the racks  23  ard  24  such that the flat beam always impinges a vertical array of the detectors  8  of X-radiation which the receptor  3  is comprised of The body  6  being scanned, possibly the human&#39;s body, referred to for the case described as “a passenger” is positioned onto the carrier  5  from it&#39;s first side. A safeguard  30  provides a support for the passenger when the carrier  5  is being moved and prevents his/her possible accidental falling from the moving carrier  5 . A separate motor which may be an electric motor (not shown) provides movement of the carrier between the rack  23  and  24  in such a way that the passenger  6  traverses said flat vertical beam of X-radiation in such a way that horizontal plane transversing the bottom portion of the body i.e. the upper surface of the carrier  5  cuts off the beam by 2–5°. A beam of X-radiation transmitted by the passenger&#39;s  6  body impinges at each given scanning instant the device  9  which may be of scintillation type, and it is converted into visible light. This light is trapped by the devices  10  closely adjoining the devices  9 , and it is converted into digital electronic signals. Output digital electronic signals are fed via an interface unit  12  to the device  13  for information processing. The passenger  6  having passed through the apparatus steps down from the carrier  5  at it&#39;s second side which is opposed to the first side (see  FIG. 7 ). 
     The effective dose when examining people with an apparatus for nonmedical application is the most critical characteristic parameter. The calculation of doses in examining the human&#39;s body by directing X-rays through it at present is provided exclusively in medical radiological examination of the patients. A number of computer programs have been designed in various countries of the world exactly for medical radiology. The effective dose for examination of humans with an apparatus for nonmedical application filed has been approximately evaluated by means of known apparatus and methods. 
     For determination of the incoming dose the phantom of Alderson-Rando was used as well as the kit “N OMEX” of PTW-Freiburg (Germany) Company, the latter being comprised of a flat ionization chamber type 77335 with the total volume of 112 cm 3 . 
     The energy range of the chamber calibration was within from 39 keV to 95 keV with the correction factor being decreased from 1.04 to 0.99. 
     For carrying measurements on an apparatus for nonmedical application the use was made of a complex filter 6 mm A1+0.5 mm Cu. The tube voltage was varied from 120 to 200 kV. The effective radiation energy was varied from approximately 70 to 120 keV. The correction factor for the energy dependence of the chamber sensitivity K q  was considered as equal to 1. 
     The measurement results are given in Table 1. 
     
       
         
               
               
               
             
               
               
               
             
           
               
                 TABLE 1 
               
               
                   
               
               
                 Tube voltage, kV 
                 Tube current mA 
                 Air kerma μ Gy 
               
               
                 1 
                 2 
                 3 
               
               
                   
               
             
             
               
                   
               
             
          
           
               
                   
                 Chamber positioned at chest 
                   
               
               
                   
                 level of phantom 
               
               
                 120 
                 1 
                 0,375 
               
               
                   
                   
                 0,351 
               
               
                   
                   
                 0,354 
               
               
                   
                   
                 0,357 
               
               
                 120 
                 2 
                 0,612 
               
               
                   
                   
                 0,612 
               
               
                   
                   
                 0,624 
               
               
                 120 
                 3 
                 1,002 
               
               
                   
                   
                 0,999 
               
               
                   
                   
                 1,029 
               
               
                 120 
                 4 
                 1,338 
               
               
                   
                   
                 1,350 
               
               
                   
                   
                 1,359 
               
               
                 120 
                 5 
                 1,611 
               
               
                   
                   
                 1,623 
               
               
                   
                   
                 1,638 
               
               
                 120 
                 7 
                 2,268 
               
               
                   
                   
                 2,277 
               
               
                   
                   
                 2,289 
               
               
                 130 
                 1 
                 0,438 
               
               
                   
                   
                 0,438 
               
               
                   
                   
                 0,426 
               
               
                 130 
                 2 
                 0,804 
               
               
                   
                   
                 0,804 
               
               
                   
                   
                 0,801 
               
               
                 130 
                 3 
                 1,275 
               
               
                   
                   
                 1,290 
               
               
                   
                   
                 1,278 
               
               
                 130 
                 4 
                 1,701 
               
               
                   
                   
                 1,722 
               
               
                   
                   
                 1,719 
               
               
                 130 
                 5 
                 2,094 
               
               
                   
                   
                 2,094 
               
               
                   
                   
                 2,097 
               
               
                   
                   
                 2,100 
               
               
                 130 
                 6 
                 2,520 
               
               
                   
                   
                 2,532 
               
               
                   
                   
                 2,524 
               
               
                 140 
                 1 
                 0,519 
               
               
                   
                   
                 0,516 
               
               
                   
                   
                 0,519 
               
               
                 140 
                 2 
                 1,002 
               
               
                   
                   
                 1,002 
               
               
                 140 
                 3 
                 1,611 
               
               
                   
                   
                 1,611 
               
               
                 140 
                 4 
                 2,163 
               
               
                   
                   
                 2,172 
               
               
                 140 
                 5 
                 2,607 
               
               
                   
                   
                 2,628 
               
               
                 140 
                 6 
                 3,108 
               
               
                   
                   
                 3,129 
               
               
                 150 
                 1 
                 0,648 
               
               
                   
                   
                 0,654 
               
               
                 150 
                 2 
                 1,224 
               
               
                   
                   
                 1,233 
               
               
                 150 
                 3 
                 1,983 
               
               
                   
                   
                 1,938 
               
               
                 150 
                 4 
                 2,661 
               
               
                   
                   
                 2,655 
               
               
                 150 
                 5 
                 3,243 
               
               
                   
                   
                 3,273 
               
               
                 160 
                 1 
                 0,741 
               
               
                   
                   
                 0,759 
               
               
                 160 
                 2 
                 1,404 
               
               
                   
                   
                 1,461 
               
               
                   
                   
                 1,452 
               
               
                 160 
                 3 
                 2,331 
               
               
                   
                   
                 2,337 
               
               
                 160 
                 4 
                 3,138 
               
               
                   
                   
                 3,162 
               
               
                 160 
                 5 
                 3,870 
               
               
                   
                   
                 3,879 
               
               
                 170 
                 1 
                 0,885 
               
               
                   
                   
                 0,885 
               
               
                 170 
                 2 
                 1,725 
               
               
                   
                   
                 1,728 
               
               
                 170 
                 3 
                 2,730 
               
               
                   
                   
                 2,784 
               
               
                 170 
                 4 
                 3,705 
               
               
                   
                   
                 3,753 
               
               
                 170 
                 5 
                 4,569 
               
               
                   
                   
                 4,563 
               
               
                 180 
                 1 
                 1,011 
               
               
                   
                   
                 1,002 
               
               
                 180 
                 2 
                 1,962 
               
               
                   
                   
                 1,953 
               
               
                 180 
                 3 
                 3,171 
               
               
                   
                   
                 3,171 
               
               
                 180 
                 4 
                 4,266 
               
               
                   
                   
                 4,275 
               
               
                 180 
                 5 
                 5,259 
               
               
                   
                   
                 5,262 
               
               
                 190 
                 1 
                 1,206 
               
               
                   
                   
                 1,212 
               
               
                 190 
                 2 
                 2,310 
               
               
                   
                   
                 2,301 
               
               
                 190 
                 3 
                 3,657 
               
               
                   
                   
                 3,672 
               
               
                 190 
                 4 
                 4,956 
               
               
                   
                   
                 4,998 
               
               
                 200 
                 1 
                 1,392 
               
               
                   
                   
                 1,398 
               
               
                 200 
                 2 
                 2,652 
               
               
                   
                   
                 2,643 
               
               
                 200 
                 3 
                 4,209 
               
               
                   
                   
                 4,212 
               
               
                   
                 Background measurement 
               
               
                 0 
                 0 
                 0,033 
               
               
                   
                   
                 0,030 
               
               
                   
                 Measurement behind phantom 
               
               
                   
                 Chamber at chest level 
               
               
                 190 
                 4 
                 0,450 
               
               
                   
                   
                 0,462 
               
               
                 150 
                 3 
                 0,183 
               
               
                   
                   
                 0,189 
               
               
                   
                 Chamber at stomach level 
               
               
                 150 
                 3 
                 2,247 
               
               
                   
                   
                 2,250 
               
               
                 190 
                 2 
                 2,610 
               
               
                   
                   
                 2,652 
               
               
                   
                 Chamber at head level 
               
               
                 150 
                 3 
                 1,443 
               
               
                   
                   
                 1,428 
               
               
                 190 
                 2 
                 1,566 
               
               
                   
                   
                 1,752 
               
               
                   
               
             
          
         
       
     
     The study of the data received reveals that the doses in the bottom part of the body appeared to be higher than at head level. This can be explained by the fact that the source of irradiation was positioned at the distance of about 40 cm relative to the floor, and the source-to-object distance in the bottom part of the body appears to be less than in the upper part. 
     The calculation of effective dose was carried out by means of program “ORGDOSA” which is analogous to program PDS-60. 
     Since the program was designed for determination of an affective dose during medical X-ray examination, the radiation conditions on an apparatus for nonmedical application filed appear to be beyond the range of specifications covered by the program. 
     Generally speaking the limitations of specifications in the program do not differ from those in the dose measuring instruments i.e. source-to-object distance of not more than 200 cm, maximum tube voltage value 150 kV, minimum incoming dose 10μ Gy etc. Therefore for calculation of an effective dose the well-known laws of physics concerning the interaction of an X-ray radiation with the substance were to be taken into account, i.e.:
         1. With one and the same filter the increase of tube voltage results in the decrease of the incoming dose;   2. The increase of the source-to-object distance under the constant specifications of the tube results in the decrease of the incoming dose;   3. The program does not provide an X-ray examination of the whole body, therefore to make calculations the radiation field was divided into separate components i.e. head, chest, stomach, pelvis and hips with the calculation of the effective dose for the whole of the body from each component and further summing up of the results thus received. No contribution from ankles and foot to the total dose was accounted as the phantom of Alderson-Rando does not possess these, and the measurements at this level were not made.       

     4. The calculation was carried out for minimum incoming dose recorded in the program which was of 10μ Gy with further equating of an amount of the effective dose to the measured input dose at the level considered. 
     An example of calculating the effective dose under X-ray examination of the phantom of Anderson-Rando by means of an apparatus for nonmedical application filed.
         Tube voltage-150 kV.   Tube current-3 mA.   Distance of source-to-object input surface-20 cm.   Radiation field dimensions-chosen for each level i.e. head, chest, stomach, pelvis and hips.   Deff=0.11μ Sv for head,   Deff=1.04μ Sv for chest,   Deff=1.19μ Sv for stomach,   Deff=1.13μ Sv for pelvis,   Deff=0.76μ Sv for hips,   Deff=4.23μ Sv total.       

     Thus, the effective dose for examination of humans with an apparatus for nonmedical application filed may be approximately evaluated as the one not exceeding 5μ Sv for any conditions of X-ray examination within the range of tube voltages not exceeding 150 kV and tube currents not exceeding 3 mA. However, the results thus received should be considered as particularly preliminary ones. 
     Due to the X-ray beam scattering angle in the vertical plane of 37–43° and low positioning of the source  4  of X-radiation such that the upper surface of the carrier  5  cuts off the beam by 2–5′ the carrier  5  during just a single movement makes it possible to provide full scanning of the passenger&#39;s body  6  on the whole from the head to the shoes with identification therein or thereon of certain foreign articles. 
     The tilt of the upper part of the receptor  3  by 4–6° towards the carrier  5  provides for the compensation of the extension of the path of X-radiation up to this part of the receptor  3  and thus makes it possible to eliminate the impairment of the image quality of the upper portion of the body. 
     As it is seen in  FIGS. 4–7 , the height of this modification of an apparatus must be made min. 2,5 m to provide the examination of passengers of any height. However a n-shaped structure of such dimensions appears to be greatly sensitive to vibrations and environmental changes such as temperature etc. At temperature changes the structure will warp, this causing displacement of a flat beam from the linear receptor  3 . To eliminate this effect the upper bar of the holder has been made as described above (see  FIG. 6 ). The rods  27  provide redistribution of the tensions thus created into the four flat rectangular plates  29 , which in turn redistribute and damp said tensions therein. 
     The detector  8  of X-radiation comprises an interrogation pulse generator  31 , a radiation sensitive element  9  (for the first embodiment of the detector filed it is a photodiode), a key transistor  32 , a load  33 . In accordance with the second and the third embodiments the detector may also comprise a current-limiting resistor  34 . In accordance with the first embodiment of the detector (see  FIG. 8 ,  9 ,  10 ) the pliotodiode  9  and the load  33  are connected in series while the load  33  is connected by its signal output to the photodiode  9  and by the other end to a common bar. The second electrode of the photodiode  9  is connected to the first electrode (e.g. the emitter) of the key transistor  32 , while the control electrode (e.g. the base) is connected via a resistor  35  to the output of the interrogation pulse generator  31  and the third electrode of the transistor  32  (e.g. the collector) is connected to the common bus. An integrating capacitor  36  may be connected in parallel to the photodiode  9 . In the second modification of the first embodiment of the detector (see  FIG. 9 ) the load  33  is connected in parallel to N groups of  37   1 ,  37   2 , . . .  37   N  components, each of said groups comprising seriesly connected the key transistor  32  and the photodiode  9  with the possibility of parallel connection to the latter of the integrating capacitor  34 . Besides, the interrogation pulse generator  3  comprises N outputs, each of the latter being connected via the resistor  35  to the control electrode (the base) of the key transistor  32  from the respective group of components where N is an integer more than 1. In the third modification of the first embodiment of the detector (see  FIG. 10 ) L loads  31   1 ,  32   2 , . . .  31   L  are used with Ni said groups of components being connected in parallel to an i-numbered load, and the interrogation pulse generator  31  contains M outputs where M=ΣN i  and L, Ni are the integers more than 1. 
     In the second embodiment of the detector filed (see  FIG. 11 ,  12 ,  13 ,  14 ) it is possible to use as sensitive elements  9  besides photodiodes also other types of components such as ionization chambers for instance (see  FIG. 11 ) or proportional counters of ionizing radiation (see  FIG. 12 ,  13 ,  14 ). The detector filed (see  FIG. 11 ,  12 ) in its first most ordinary modification of the second embodiment comprises the interrogation pulse generator  29 , a radiation sensitive element  9 , a key transistor  32 , a load  33 , a current-limiting resistor  32 , and an intergrating capacitor  34 . 
     In this combination a radiation sensitive element  9  is connected on the one end to a power supply bus and on the other end via the current-limiting resistor  34  to the first electrode (e.g. the drain or the emitter) of the key transistor  32  and to the first plate of the integrating capacitor  36  with the second plate of said capacitor being connected to the common bus. Besides, the output of the interrogation pulse generator  31  is connected to the control electrode (the gate or the base) of the key transistor  32 . Should the key transistor  32  be a bipolar one, then there is connected a resistor  35  between the output of the generator  31  and the base of the transistor  32  (see  FIG. 12 ). The third electrode (e.g. the source or the collector) of the key transistor  32  is connected to the common bus. The power supply bus is fed with constant voltage Ec of the appropriate polarity and value. Both field-effect transistors (see  FIG. 11 ) and bipolar transistors (see  FIG. 12 ) may be used as the key transistor  32 . 
     It is most feasible to use in the second embodiment of the detector filed the elements which are sensitive to various types of radiation, said elements demanding for their efficient operation the supply of a bias voltage including a high-tension one. In the second modification of the second embodiment of the radiation detector filed (see  FIG. 13 ) between a power supply bus and a common bus there are connected N groups of  37   1 ,  37   i , . . .  37   N  components, each of said groups being comprised of a seriesly connected radiation sensitive element  9  and a key transistor  32  with the common point of these being connected via an integrating capacitor  36  to the signal output of a load  33 . Besides an interrogation pulse generator  31  contains N outputs with each of said outputs being connected via a resistor  35  to the control electrode (the base) of the key transistor  32  from the respective group of components where N is an integer more than 1. In the third modification of the second embodiment of the radiation detector (see  FIG. 14 ) there is contained L loads  31   1 ,  31   2 , . . .  31   L , with the signal output of each i-numbered load being connected to Ni of above said groups of components, and an interrogation pulse generator contains M outputs where M=ΣNi and Li Ni are the integers more than 1. 
     In the third embodiment of the radiation detector filed (see  FIG. 15 ,  16 ) there is also provided the possibility of using besides the photodiodes of other types of sensitive elements  9  which demand for their efficient operation the supply of a bias voltage, for instance for the photoresistors (see  FIG. 15 ). In the first most comprehensive modification of the third embodiment of the detector filed (see  FIG. 15 ) there is contained a interrogation pulse generator  29 , a radiation sensitive element  9 , a key transistor  32 , a load  33  and a current-limiting resistor  34 . In this combination the radiation sensitive element is connected on the one end to a power supply bus and on the other end via the current-limiting resistor  34  to the first electrode (e.g. the drain) of the key transistor  32 . The output of the interrogation pulse generator  31  is connected to the control electrode (e.g. the gate) of the key transistor  32 , with the third electrode (e.g. the source) being connected to the signal output of the load  33  which is connected on the other side to the common bus. The power supply bus is fed with constant voltage Ec of the appropriate polarity and value. The second modification of the third embodiment of the radiation detector filed (see  FIG. 16 ) additionally contains an integrating capacitor  34 , which is connected between the first electrode (e.g. the drain) of the key transistor  32  and the common bus. The key transistor  32  in the third embodiment of the radiation detector filed must be exclusively of the field-effect type with the internal capacitance of this type of transistors being used as an integrating one in the first modification of this embodiment of the detector. 
     The interrogation pulse generator  31  in the radiation detector filed presents in itself a generator of rectangular tension pulses. The amplitude and the polarity of the voltage output pulses are chosen such that they could provide a turn-on mode of the respective key transistors of the detector. Multi-component modifications of the detector may employ as the generator  29  ring counters, deciphers, shift registers and other devices with the number of outputs of said devices being equal to the number of key transistors in the detector and the voltage pulses of the appropriate polarity amplitude and duration being generated at said outputs at respective time instants. 
     The operation of the radiation detector is provided in the following way. The current of the sensitive element  9  which is generated under the influence of the radiation is integrated by the common capacitance of the sensitive element  9  and parallel connected integrating capacitor  36  (see  FIG. 8 ,  9 ,  10 ), by the capacitance of the integrating capacitor  36  (see  FIGS. 11–14 ), by the internal capacitance of the key transistor  32  and the integrating capacitor  36  (see  FIG. 16 ) during the period between the interrogations of the transistor  32 . During the interrogation instant of the key transistor  32  an interrogation pulse is supplied from the output of the generator  31  to the control electrode of the transistor  32  with the polarity of said pulse providing the turn-on of the transistor  32 . As a result of the turn-on of the transistor  32  the latter starts to conduct a current pulse which transfers a charge via the capacitor  36  and the load  33 , said charge having been integrated by the capacitor  36  (and also by the capacitance of the sensitive element  9  or by the capacitance of the transistor  32 ). Concurrently with supplying the interrogation pulse the load  31  starts to pass the charges used to recharge the interelectrode capacitances of the transistor  32  via the capacitance of the sensitive element  9  and/or the integrating capacitor  36  (see  FIGS. 8–14 ) or directly (see  FIG. 15 ,  16 ). The charges of the same value but having the reverse polarity are coupled via said chains during takeoff of the interrogation pulse. As a result after supplying of each interrogation pulse the load  33  passes a total charge equal to the charge of the current of the sensitive element  9  which has been integrated by the capacitor  36  and/or proper capacitance of said sensitive element during the time between supplying of the interrogation pulses. Should the load  33  be connected between the key transistor  32  and the common bus (see  FIGS. 15 ,  16 ), then after supplying of the interrogation pulse the current charge of the sensitive element  9  which has been integrated by the total capacitance of the capacitor  36  and/or the transistor  32  is transferred to the load  33 . This charge is proportional to the flow of radiation which has been impinging the sensitive element  9  during the time between interrogations of the respective key transistor  32 . 
     The interrogation pulse generator  31  used in multi-component modifications of the detector filed (see  FIGS. 9 ,  10 ,  13 ,  14 ) is provided with a plurality of outputs with the tension pulses being generated at each of said outputs in a pre-defined sequence. During this operation there comes a sequential interrogation of the key transistors  30 , which the group  37  of components is comprised of, this interrogation corresponding for instance to the coming in turn read-out of the respective integrating capacitor  36  with the current pulses being generated at the load, said pulses when added at respective time instants by the sync pulses could be presented as a videosignal, while the coordinate of the detector sensitive element is always defined by the number of corresponding to it pulse at the load or by the instant of the appearance of said pulse with the number of radiation particles which have been registered in this sensitive element being defined by the amplitude of the current pulse corresponding to said element. A series of readout current pulses in the modifications of the detector with several loads (see  FIGS. 10 ,  14 ) is generated in turn at each of the loads during the interrogation time of the key transistors included in the groups  37  of the components coupled to said load. The use of several loads in the detector makes it possible to increase the total number of the sensitive elements in the detector without increasing the noise of the readout registrating signals of the amplifiers&#39; integrating capacitor. The ability of the detector filed apart from its increased sensitivity at registration of the radiation also to make the analysis of the space-energy characteristics of the various kinds of radiation studied in the wide range of the intensities makes it possible to substantially expand its operating possibilities and the field of application. 
     The receptor which has been designed using the detectors described and which can operate with the extra small charges provides a one-step analog-to-digital conversion. The combination of a highly efficient pair of the scintillator and the photodiode alongside with the schematic solution filed increases the sensitivity and precision at registrating the intensities of X-radiation and also expands the dynamic range of the X-radiation intensities being registered. 
     This in its turn provides the possibility to substantially decrease the dose of X-radiation during examination and to improve the quality of X-ray images. The use of the technical solutions filed makes it possible to conduct safe X-ray examinations not only of people suffering from various diseases (the patients), but also of a large number of healthy people, the passengers for example. 
     The present invention is not limited by the above-mentioned examples.