a ct apparatus of the 3rd generation suitable for implementation of the inventive method is shown in fig1 but without , among other things , a housing frame . the scanning unit or measurement of the ct apparatus ( designated overall with 1 ) has an x - ray source 2 and a detector system 5 fashioned as a laminar array of a number of rows and columns of detector elements 4 . the x - ray source 2 and the detector system 5 are mounted opposite one another on a rotating frame ( not shown ), such that a pyramidal x - ray beam with edge rays 8 , emanating ( in the operation of the ct apparatus ) from the x - ray source 2 and gated by adjustable ray diaphragms , strikes on the detector system 5 . the rotating frame ( gantry ) can be displaced in rotation around a system axis z by means of the actuation device 7 fashioned as a synchronous motor or alternatively as an asynchronous motor with a belt drive . the system axis z runs parallel to the z - axis of a spatially - rectangular coordinate system shown in fig1 . the columns of the detector system 5 likewise run in the direction of the z - axis while the rows ( whose width b is measured in the direction of the z - axis and is , for example , 1 mm ) run transverse to the system axis z and the z - axis . in order to be able to bring an examination subject ( for example a patient ) into the beam path of the x - ray beam , a bearing device 9 is provided that can be moved parallel to the system axis z , thus in the direction of the z - axis with a synchronization between the rotation movement of the rotating frame and the translation movement of the bearing device 9 in the sense that the ratio of translation speed to rotation speed is constant . this ratio can be adjusted by a desired value for the feed h of the bearing device 9 per rotation of the rotating frame being selected . a volume of an examination subject located on the bearing device 9 thus can be examined in the course of a volume scan , the volume scan being effected in the form of a spiral scan in the sense that a number of projections be acquired from various projection directions with simultaneous rotation of the scanning unit 1 and translation of the bearing device 9 with the set ratio by means of the scanning unit 1 per revolution of the scanning unit 1 . in the spiral scan , the focus f of the x - ray source moves on a spiral path s relative to the bearing device 9 . the measurement data are read out in parallel from the detector elements 4 of each row of the detector system 5 during the spiral scan and , corresponding to the individual projections , are serialized in a sequencer 10 and transferred to an image computer 11 . after pre - processing of the measurement data in a pre - processing unit 12 of the image computer 11 , the resulting data stream arrives at a cross - section reconstruction unit 13 that reconstructs from the measurement data slice images of desired slices of the examination subject according to a known method ( for example 180li or 360li interpolation ). in order to be able to determine the position of the slice ( for which a cross - section should be reconstructed ) in the z - direction , an x - ray shadow image can also be reconstructed in addition to cross - sections . for this , the portion of the measurement data necessary for reconstruction of an x - ray shadow image is extracted from the data stream coming from the sequencer 10 by a filter 14 , and before the data stream arrives at the cross - section reconstruction unit 13 . this data portion is supplied to an x - ray shadow image reconstruction unit 15 that reconstructs an x - ray shadow image from the extracted measurement data according to a known method . the section or x - ray shadow images reconstructed respectively by the cross - section reconstruction unit 13 and the x - ray shadow image reconstruction unit 15 during the implementation of the spiral scan are shown parallel to and synchronous with the spiral scan on a display unit 16 ( for example a video monitor ) connected to the image computer 11 . the x - ray source 2 , for example an x - ray tube , is supplied with the necessary voltages and currents by a generator unit 17 . in order to be able to adjust these to the respectively necessary values , a control device 18 with keyboard 19 is associated with the generator unit 17 , which control device 18 allows the necessary adjustments . the generator unit 17 also allows an intermittent or pulse - like emission of x - rays at predeterminable angle positions of the x - ray source 2 . the angle positions ( projection directions ) are generated by a position sensor with an encoder . the further operation and control of the ct apparatus ensue via the control device 18 and the keyboard 19 , which is illustrated by the control device 18 is connected with the image computer 11 . the control device 18 , moreover , serves for the activation of the drive device 7 . the design of the image computer 11 has been described above based on hardware components , namely the pre - processing unit 12 , the cross - section reconstruction unit 13 , the filter 14 and the x - ray shadow image reconstruction unit 15 . normally , however , the cited components are realized by software modules that run on a universal computer provided with the necessary interfaces . the universal computer can also ( deviating from fig1 ) assume the function of the control device 18 . the generator unit 17 and the drive device 7 allow the following operating modes to be set by the control unit 18 : v : continuous operation of the x - ray source 2 in volume scanning , for example spiral scanning , with an x - ray power parameterized for the generation of slice images , t ′: continuous operation of x - ray source 2 in spiral scanning with an x - ray power parameterized for the generation of x - ray shadow images ( topogram ) and reduced relative to the operating mode “ v ”, t : activated operation of the x - ray source 2 , whereby the x - ray source 2 radiates an x - ray pulse with the x - ray power parameterized for the generation of x - ray shadow images only when the rotating x - ray source 2 is located in a position corresponding to the desired projection direction for he x - ray shadow image ( topogram ), and a : disconnected operation , in which the x - ray source 2 does in fact rotate with constant rotation frequency f a (& gt ; 0 , for example 1 rotation / s ) (“ standby mode ”) but is not activated . fig2 and 3 shows a simplified flowchart or time diagram of the workflow in the examination of a number of examination subjects u 1 , u 2 , etc . ( the examination subjects as such are not shown ) fig2 schematically shows the curve of the rotation frequency f rot with the time t during the workflow . the t - axis is not scaled linearly : generally a spiral scan will take longer , in comparison with a topogram acquisition , than as shown here . a calibration step “ cal ” is executed at the beginning of a workday or a work week . the control device 18 subsequently brings the scanning unit 1 into rotation in a first park or standby phase 21 with the operating mode “ a ” in which the ct apparatus remains available until a first examination subject u 1 for examination . in the operating step “ t ”, the examination is then begun with a topogram step 22 without interruption of the rotation . only an x - ray shadow image ( topogram ) of the first examination subject u 1 — or alternatively two shadow images laterally and a . p . are reconstructed and displayed . without interruption of the rotation , in a further standby phase 23 the apparatus is subsequently switched again into the operating mode “ a ” during which the operating personnel initially establishes a diagnostically - relevant scan region and then , using this , positions the first examination subject u 1 at the beginning of the desired scan region . after the positioning has occurred , a spiral scan is implemented with continuous rotation in the operating mode “ v ” in a volume scan step 24 with rotation speed negligibly increased relative to step 23 . when the prior established end of the scan region is reached , without interruption of the rotation the scanning unit 1 is switched again into the operating mode “ a ” in a further standby phase 25 and the radiation is deactivated , but the scanning unit 1 still rotates . the ct apparatus remains in this state until a further patient should be examined . the procedure is subsequently repeated as needed with a second examination subject u 2 , but in the example a different region of the patient is to be examined ( different application ): topogram step 26 , standby phase 27 with positioning of the second examination subject u 2 for the subsequently volume scan 28 with a rotation frequency less — due to the different application — in comparison to the examination of the first examination subject u 1 , standby phase 29 . the cycles are subsequently repeated again with further examination subjects , with the scanning unit 1 rotating without interruption over a time span δt of a plurality of hours . the scanning unit 1 can also rotate during the calibration step cal , which is different than shown in fig2 and 3 . as an alternative to the operating mode “ t ”, at the beginning of the examination parallel x - ray shadow image reconstruction and cross - section image reconstruction can be implemented in the operating mode “ t ′”. the results are shown in parallel on the display unit 16 . due to the reduced x - ray power , however , the cross - sections can be diagnostically used only in a limited manner . in the implementations described with fig2 and 3 , it was assumed that the topogram is completely concluded before the actual volume scan , and that both beginning and end of the diagnostically - relevant scan region are thus known . as an alternative , the topogram can be generated only in part before the volume scan is begun : namely , if diagnostically - relevant structures are reached in the operating mode “ t ′” or “ t ” with increasing z - feed of the scanning unit 1 , the scanning unit 1 can be switched to the operating mode “ v ” without interruption of the rotation , in which operating mode “ v ” measurement data are now acquired that ( due to the now - higher x - ray power ) enable reconstruction of slice images of higher quality that are simultaneously displayed with the x - ray shadow image . after the diagnostically - relevant region has been scanned , in this alternative the scanning unit 1 is switched again into the operating mode “ a ” in a further standby phase 25 without interruption of the rotation of the scanning unit 1 and the radiation is deactivated , but the scanning unit 1 still rotates further . in a further alternative operating mode that is particularly of importance for ct apparatuses having a detector system 5 that exhibits a large width in the direction of the system axis z and thus has a large number of rows , a relative movement between the scanning unit 1 and the bearing device 9 in the direction of the system axis z ( a spiral scan ) can be foregone if the extent of the detector system 5 is sufficient to acquire the entire region to be examined . for the case that the extent of the detector system 5 in the direction of the system axis z is greater than the corresponding extent of the region to be examined , it is sufficient to activate only those rows the detector system 5 that are necessary for acquisition of the examined region . conventionally , the rotation operation of the rotating mass in an x - ray computed tomography ( ct ) apparatus would have to fulfill two criteria : 1 . a precise adjustment of the rotation frequency according to specification and 2 . a positioning of the mass at a specific angle position for balancing . in terms of regulation technology , both requirements are very difficult to fulfill together , so that in the past the rotation speed regulation , which is decisive for the imaging in a spiral scan , would often have to take precedence . with only a simple mass positioning method , a number of attempts ( for example by braking the mass with a correction angle and studying the braking path ), and therewith more time , could be necessary in order to achieve the goal . in the individual case , the angle precision would amount to only approximately +/− 5 °. a ) only a constant rotation speed must still be regulated , i . e . the regulation system can be executed comparably simply and the actuator can be reduced , for example , to a very inexpensive asynchronous motor , and that b ) the precision of the angle adjustment for a topogram is significantly higher , thus the subdivision of an angle of the rotation position transmitter ( and therewith the result of the generated overview image ) is more precise . a continuously - rotating measurement system also achieves a uniform temperature distribution and thereby allows an increased measurement precision , thus a better image quality . a continuously - rotating measurement system prevents “ temperature peaks ”, i . e . locally pronounced temperature increases that can cause mechanical warpings of the measurement system , thereby producing measurement inaccuracies , for example via distortion of the beam fan relative to the detector , and / or can lead to increased mechanical wear , for example of a bearing . a continuous rotation also allows the rotating measurement system to be shaped such that it is actively participating in the cooling , for example , by the mounting or the rotating frame 40 of the measurement system being designed so that it acts as an air mover . for this purpose — as shown schematically in fig4 — air scoops 43 can be present on the outside ( front side or circumferential side ) of a housing 41 of the rotating frame 40 as a part of a cooling device 42 . the air current required for cooling during operation can then be generated without additional components . to prevent injuries , the air scoops 43 can be covered either by the frame 45 of the ct apparatus or by a special covering ( mesh network etc .) the invention can be applied in fields outside of medicine as well , for example in package inspection or in material examination . although modifications and changes may be suggested by those skilled in the art , it is the invention of the inventor to embody within the patent warranted heron all changes and modifications as reasonably and properly come within the scope of his contribution to the art .
in a continuously operating tomography apparatus and an operating method therefore , a scanner unit is rotated around a system axis and first and second examination subjects are successively moved into the scanner unit and respective examinations of the first and second examination subjects are conducted without interruption of rotation of the scanner unit . the rotation frequency of the scanning unit is set differently dependent on the type of examination to be conducted , and when no examination of an examination subject is taking place , the scanning unit is rotated at a predetermined rest rotation frequency , that is smaller than a smallest of the available rotation frequencies for the examinations , or is an average of the rotation frequencies available for the examinations .