hereinafter , referring to the accompanying drawings , embodiments of the present invention will be explained . fig1 shows the configuration of a circuit for supplying power from the static gantry section to the rotatable gantry section in an x - ray ct apparatus according to a first embodiment of the present invention . fig2 is a sectional view showing the location of the individual parts inside the static gantry section and rotatable gantry section . as shown in fig1 the x - ray ct apparatus of the first embodiment is composed of a static gantry section 12 and a rotatable gantry section 22 roughly divided as shown by broken lines . the static gantry section 12 includes an alternating - current ( a . c .) power generator section 13 composed of an a . c . power source 11 , an ac / dc converter 14 , and an inverter 15 and a transformer fixing section 51 . the rotatable gantry section 22 includes a transformer rotating section 52 , a rectifier 20 , and an x - ray tube 21 . the transformer fixing section 51 provided on the static gantry section 12 and the transformer rotating section 52 provided on the rotatable gantry section 22 constitute a separate - type high - voltage transformer 50 . the transformer fixing section 51 includes a primary coil 16 and a primary side core 17 . the transformer rotating section 52 includes a secondary coil 19 and a secondary side core 18 . the primary side core 17 is not formed integrally with the secondary side core 18 . the arrangement of the primary side core 17 and secondary side core 18 will be explained in a second embodiment of the present invention . the ac / dc converter 14 is connected to the output terminal of the alternating - current ( a . c .) power source 11 serving as an input power source . a plurality of inverters 15 are connected in parallel with the output terminal of the ac / dc converter 14 . the output terminal of each of the inverters 15 is connected to the primary coil 16 of the transformer fixing section 16 . the ac / dc converter 14 converts the a . c . voltage from the a . c . power source 11 into a direct - current ( d . c .) voltage . the d . c . voltage is then supplied to the inverter 15 , which converts the d . c . voltage into a high - frequency a . c . voltage . the reason why a plurality of inverters 15 are used in fig1 is to prevent the whole of the x - ray ct apparatus from stopping the operation if one of the inverters 15 fails . by selecting the troubled inverter 15 and stopping it , the power can be controlled roughly . for the convenience of design , only one inverter 15 may be provided . the high frequency a . c . power generator 13 may have another configuration , as long as it generates power of desired frequency , for example , about 100 khz . the output of the high frequency a . c . power generator 13 is connected to the primary coil 16 . when a plurality of inverters 15 are used , such as this embodiment , the output of each of the plurality of converters 15 is provided to the respective primary coils 16 . alternatively , if only one inverter 15 is used , the output of the inverter 15 is parallelly connected to a plurality of primary coils 16 . as shown in fig2 the static gantry section 12 is mounted on a base 60 . near the static gantry section 12 , the a . c . power source 11 is provided . the static gantry section 12 has an opening 101 . along to the cylindrical direction on outside of the opening 101 , the inverter 15 , primary coil 16 , primary side core 17 , and others are arranged . a doughnut - like disk rotatable gantry section 22 with an opening 100 in it is provided on the static gantry section 12 in such a manner that it can rotate continuously . the top 120 is inserted into the opening 101 of the static gantry section 12 and the opening 100 of the rotatable gantry section 22 . outside the opening 100 of the rotatable gantry section 22 , the secondary side core 18 , secondary coil 19 , rectifier 20 , and others are arranged . the x - ray tube 21 and x - ray detector 32 are provided on the rotatable gantry section 22 in such a manner that they face each other with the opening 100 between them . the primary coil 16 is wound around almost the central part of the primary side core 17 . two primary coils 16 may be wound around one primary coil 17 . the primary coil 16 and the primary side core 17 are arranged around the static gantry section 12 so that the magnetic flux generated at the primary side core 17 may be supplied to the rotatable gantry section 22 . the shape of the primary 17 is not limited to the squared - u shape . as long as the magnetic flux generated at the primary side core 17 , together with the secondary side core 18 arranged so as to face the primary side core 17 , can form a magnetic circuit , the primary side core may take another shape . the squared - u - shaped secondary side core 18 facing the primary side core 17 is arranged around the ringed rotatable gantry section 22 placed so as to surround the top 120 of the couch , as is the primary side core 17 . in this case , too , the secondary side core 18 may take another shape , as long as it , together with the primary side core 17 , can form a magnetic circuit . the secondary coil 19 is wound around almost the central portion of the secondary side core 18 . as shown in fig1 a capacitor 24 is connected in series with the secondary coil 19 . the secondary capacitor 24 is designed to resonate with the inductance of the secondary coil 19 . the inductance of the secondary coil 19 makes the impedance higher as the frequency increases , which is one of the factors that hinder the high - frequency operation most . when a suitable value of the secondary capacitor is selected , the secondary impedance can be adjusted by resonance , which enables a high - frequency operation . in the conventional x - ray ct apparatus in each of fig1 and fig1 , only one secondary coil 19 was used . since the resonance voltage at the secondary coil 19 is overhigh than the necessary output voltage of 10 kv or higher , it is technically difficult to produce an insulting of the secondary coil 19 . furthermore , it is technically difficult to produce a capacitor capable of withstanding such a high voltage by itself . to overcome this drawback , the first embodiment uses a plurality of secondary coils 19 , thereby lowering the voltage generated in each secondary coil 19 . this makes it technically easy to realize an insulting of the secondary coil 19 or the capacitor 24 . the series circuit of the secondary coil 19 and capacitor 24 is connected to the rectifier 20 . although the number of rectifiers 20 is the same as that of capacitors 24 , either the number of rectifiers 20 or that of capacitors 24 may be larger than the other . the rectifiers 20 rectify high frequency a . c . power into d . c . power . the secondary side core 18 , secondary coil 19 , secondary capacitor 24 , and rectifier 20 on the rotatable gantry section 22 constitute a high - voltage unit 23 . the one - side ends of the high - voltage unit 23 are connected in series and similarly its other - side ends are connected in series . the resulting one end and other end are connected to one end and the other end of the x - ray tube 21 , respectively . the high - voltage unit 23 , x - ray tube 21 , and x - ray detector 32 are provided around the rotatable gantry section 22 , taking weight balance into account . in the conventional example , when the rotatable gantry section was rotating , the weight of the rotatable gantry section was large and developed a great centrifugal force of , for example , about 13 g , which was a factor preventing a high - speed rotating operation . in the first embodiment , however , the series resonance on the secondary side enables a high - frequency operation , for example , an operation at 100 khz , which helps make the inverter 15 , primary coil 16 , primary side core 17 , secondary coil 19 , and secondary side core 18 smaller and lighter . the smaller , lighter secondary coil 19 and secondary side core 18 particularly decrease the weight and space of the rotatable gantry section 22 remarkably . since the secondary coils 19 and the secondary side cores 18 are circularly and evenly arranged on the rotatable gantry section , the section excels at rotation balance . also , since the capacitor 24 is provided for resonance , and certain degree of the leakage inductance of the secondary coil 19 is used for the construction of the resonance circuit , there is no need to take into account the leakage inductance of the secondary coil 19 as inhibition factor . therefore , the secondary coil 19 can be wound around the secondary side core 18 with a sufficient insulting distance between them . as high a voltage as 150 kv can be generated , making it unnecessary to provide an additional high - voltage transformer for generating a high voltage on the rotatable gantry section 22 , which enables the rotatable gantry section 22 to be made smaller and thinner remarkably . because the decreased number of component parts on the rotatable gantry section makes room for the space of the rotatable gantry section , it is possible to realize an x - ray ct apparatus with multiple tubes . use of an x - ray ct apparatus with multiple tubes can improve time resolution of acquired image . hereinafter , various modifications of the circuit for supplying power from the static gantry section to the rotatable gantry section in the x - ray ct apparatus according to the first embodiment will be explained . in a first modification of the first embodiment in fig3 the capacitor 24 is connected in parallel with the secondary coil 19 . the capacitor 24 resonates with the leakage inductance of the secondary coil 19 . in a secondary modification of the first embodiment in fig4 a capacitor 31 is inserted in series between the output of the high voltage a . c . power generator section 13 and the primary coil 16 . in the second modification , the capacitor 24 is provided so as to resonate with the leakage inductance of the secondary coil 19 and the primary capacitor 31 is provided so as to resonate with the inductance of the primary coil 16 . even when resonance not only on the secondary side but also on the primary side make the operating frequency higher , the primary capacitor 31 and secondary capacitor 24 can be selected according to the resonance , which enables a high - frequency operation . that is , the primary - side leakage inductance can be used effectively in the secondary modification . in a third modification of the first embodiment , the capacitor 31 is inserted in series between the output of the high frequency a . c . power generator 13 and the primary coil 16 and the capacitor 24 is connected in parallel with the secondary coil 19 . in a fourth modification of the first embodiment , the capacitor 31 is inserted in parallel between the output of the high frequency a . c . power generator 13 and the primary coil 16 and the capacitor 24 is connected in parallel with the secondary coil 19 . furthermore , in a fifth modification of the first embodiment in fig7 the capacitor 31 is inserted in parallel between the output of the high frequency a . c . power generator 13 and the primary coil 16 . hereinafter , a second embodiment of the present invention will be explained . fig8 shows a detailed configuration of the transformer rotating section on the rotatable gantry section in an x - ray ct apparatus according to the second embodiment . fig9 shows the location of the transformer fixing section on the static gantry section and the transformer rotating section on the rotatable gantry section which face each other . fig1 is a perspective view showing the arrangement of the primary side core and secondary side core in a separate - type high - voltage transformer . a plurality of high - voltage unit blocks , for example , as shown in fig8 four high - voltage unit blocks b 1 to b 4 are arranged on the gantry section 22 to form a circumference as a whole . these blocks are connected electrically to each other by connectors c 1 to c 4 . one high - voltage unit block includes , for example , four high - voltage units 23 , m 1 to m 4 . this divided structure facilitates the replacement of the high - voltage units 23 . such a divided structure may be applied to the transformer fixing section of the static gantry section 12 . as shown in fig9 the primary coil 16 and primary side core 17 on the static gantry section 12 are provided so as to face the secondary coil 19 and secondary side core 18 on the rotatable gantry section 22 . the shape of and the number of the secondary side cores 18 are so determined that all of the plurality of primary side cores 17 never fail to the secondary side cores 18 , even when the rotary section ( rotatable gantry section 22 ) rotates . the spacing between the primary side core 17 and the secondary side core 18 is about 1 mm . note that the spacing is not limited 1 mm . as shown in fig1 , the primary coil 16 is wound on the primary side core 17 whose cross section perpendicular to the direction of rotation of the rotatable gantry section 22 is shaped like an almost squared u . the primary coil 16 is wound on the central part of the squared - u shape of the primary side core 17 . the primary side core 17 is so positioned that the two ends of the squared u may face the rotatable gantry section 22 and the straight line connecting the two ends be perpendicular to the direction of rotation of the rotatable gantry section 22 . the direction in which the rotatable gantry section 22 rotates at that time is shown by a thick arrow . at the ends of the squared - u shape of the primary side core 17 , there are provided two projecting sections 71 of the same shape which project in the direction opposite to the direction of rotation of the rotatable gantry section 22 . the projecting sections 71 may be made of the same material as that of the primary side core 17 or of a magnetic substance made of a material with different susceptibility . one projecting section 71 may be spaced , for example , about 1 mm apart from the projecting section 71 of the other primary side core 17 . according to this gap of 1 mm , well convertibility of the primary side cores 17 is achieved . alternatively , they may be jointed together without any gap . in this case , the leakage flux is avoided between the integral cores 17 . as shown in fig9 the secondary side core 18 is provided around the rotatable gantry section 22 so as to face the primary - side core 17 . as shown in fig1 , like the primary side core 17 , the secondary side core 18 is shaped like a squared u . on the central portion of the squared - u shape , the secondary coil 19 is wound . the secondary side core 18 is so arranged that the ends of the squared u are forced to face the static gantry section 12 and conversely the central portion of the squared u is caused to face the rotatable gantry section 22 , thereby making the straight line connecting the two ends of the squared u perpendicular to the direction of rotation of the rotatable gantry section 22 . in fig1 , only two cores on the primary side of the high - voltage transformer and only one core on its secondary side are shown . actually , however , many cores are present on each of the primary side and secondary side and form a circumference as a whole . the many secondary side cores rotate as the rotatable gantry section rotates . the shape , number , and arrangement of the primary and secondary side cores are so determined that the secondary side cores never fail to face the primary side cores . in the present embodiment , the primary side core has two near - rectangular open faces and the secondary side core has two near - square open faces , when viewed from the plane across which the primary and secondary side cores face each other . making the open faces of the secondary side core smaller than those of the primary side core enables the rotatable gantry section to be made lighter , facilitating insulation . to improve the power supply efficiency , the open faces of the secondary side core may be made larger . furthermore , the shape of the primary side core and that of the secondary side core may be made the same not only to improve the power supply efficiency but also to facilitate the manufacture . the magnetic flux generated by the current passed through the primary coil 16 reaches the open faces of the secondary side core 18 by way of the open faces ( or the ends of the squared u ) of the primary side core 17 . the magnetic field generated at that time is shown by a broken - line arrow . the magnetic flux causes the secondary coil 19 wound around the secondary side core 18 to generate current , thereby supplying power from the static gantry section 12 to the rotatable gantry section 22 . with this configuration , power can be supplied continuously , with the primary coil separate from the secondary coil . it should be noted that the flux from the primary side is easily and reliably transmitted to the secondary side according to an existence of the open face ( projecting section 71 ). as described above , with the present invention , it is possible to provide a thin - type x - ray computer tomography apparatus with a small - sized high - voltage transformer capable of supplying power and stepping up the voltage to the high voltage which is necessary for generating x - ray at the same time by a noncontacting rotary method . although no shown , it goes without saying that ripples in the high - voltage output due to the unevenness of the intensity of the magnetic coupling during rotation are removed by the negative feedback of the output voltage , as are ripples resulting from other causes . the negative feedback is effected by optical transmission or by radio . additional advantages and modifications will readily occur to those skilled in the art . therefore , the invention in its broader aspects is not limited to the specific details and representative embodiments shown and described herein . accordingly , various modifications may be made without departing from the spirit or scope of the general inventive concept as defined by the appended claims and their equivalents .
an x - ray computer tomography apparatus comprises a high - voltage transformer which performs the increase and noncontacting transmission of the power simultaneously and outputs a desired high voltage for causing x rays to be generated at the rotatable gantry section . the high - voltage transformer is divided into a primary - side which is provided on the static gantry section and to which the output of a frequency converting circuit is supplied and a secondary - side which generates a high voltage . a capacitor is connected to a secondary coil of the high - voltage transformer , thereby forming a resonance circuit .