Abstract: A device includes a first capacitive energy module and a second capacitive energy module. The first capacitive energy module comprises a first tray that is configured to house a first plurality of capacitive energy components, a first electrode, and a second electrode. The second capacitive energy module comprises a second tray that is configured to house a second plurality of capacitive energy components, a third electrode, and a fourth electrode. The first capacitive energy module is connected to the second capacitive energy module via a plug connector that makes a solid connection.

Abstract: A converter assembly has a rectifier receiving an external alternating voltage of a specified feed frequency, an inverter, and a DC link with a DC link capacitor electrically between the rectifier and the inverter. An absorption circuit, which is connected in parallel with the DC link capacitor, forms a series resonance circuit and is of low impedance at a series resonance frequency twice the feed frequency. The absorption circuit forms a parallel resonance circuit together with the DC link capacitor and has high impedance at a parallel resonance frequency. A damping absorption circuit, connected in parallel with the DC link capacitor and the absorption circuit, includes an ohmic resistor and is magnetically coupled to the absorption circuit. A voltage dropping at the absorption circuit at the parallel resonance frequency is transformed by the magnetic coupling to the damping absorption circuit. The resistor damps the parallel resonance of the absorption circuit.

Abstract: An X-ray generator is capable of reducing invalid exposure caused due to wave tails, which do not contribute to the quality of an X-ray image, by preventing the wave tails from being supplied to an X-ray tube. An X-ray imaging apparatus includes the X-ray generator and a method of reducing the invalid exposure is implemented using the X-ray generator. The X-ray generator includes an X-ray tube to generate X-rays, and a high-voltage generator to supply a voltage having a pulse waveform to the X-ray tube. The high-voltage generator includes a high-voltage tank to generate a high voltage, a switch connected to an output terminal of the high-voltage tank and turned on or off, and a resistor located outside the high-voltage tank to receive a wave tail voltage having the pulse waveform and to consume power generated due to wave tails.

Abstract: The X-ray equipment related to the embodiment is configured from a plurality of pressure rising units, a switching unit, and a switching control unit. The plurality of pressure rising units are connected to the battery unit and generate direct current voltage. The switching unit switches over the plurality of pressure rising units and supplies direct current voltage to the X-ray generating unit. The switching control unit transmits switching instructions to the switching unit for switching over the pressure rising unit after receiving voltage supply instructions with respect to the X-ray generating unit until said voltage supply instructions terminate. The switching control unit controls discharging of the condenser inside the pressure rising unit switched over by the switching instructions and the control of commencing charging of the condenser inside the pressure rising unit following termination of discharging.

Abstract: The invention relates to a collimator electrode, comprising an electrode body (81) that is provided with a central electrode aperture (82), wherein the electrode body defines an electrode height between two opposite main surfaces, and wherein the electrode body accommodates a cooling conduit (105) inside the electrode body for transferring a cooling liquid (102). The electrode body preferably has a disk shape or an oblate ring shape. The invention further relates to a collimator electrode stack for use in a charged particle beam generator, comprising a first collimator electrode and a second collimator electrode that are each provided with a cooling conduit (105) for transferring the cooling liquid (102), and a connecting conduit (110) for a liquid connection between the cooling conduits of the first and second collimator electrodes.

Abstract: A mobile X-ray apparatus that performs a stable operation even if a sudden voltage drop or momentary power interruption occurs during operation of a commercial AC power source. The mobile X-ray apparatus includes a plug for connection to a commercial AC power source, a battery charged from the commercial AC power source through the plug, a unit that operates by being supplied with electricity from the commercial AC power source connected through the plug, and a second circuit including a rectifier that supplies electricity to the unit from the battery if a voltage from the commercial AC power source falls to or below a regulated value while the unit is being operated by the electricity supply from the commercial AC power source.

Abstract: An imaging system can include an imaging capturing portion, an image processing unit, a main power supply and a supplemental power supply. The image capturing portion can include a source that emits an emission signal towards a target to be imaged, and a receiver that receives the emission signal emitted by the source. The image processing unit can receive the received emission signal from the imaging capturing portion and generate image data based on the received emission signal. The main power supply can be coupled to the imaging capturing portion and the imaging processing unit for providing operational power thereto. The supplemental power supply can be coupled to the main power supply and the imaging processing unit. The supplemental power supply can be charged by the main power supply in a first mode and provide operational power to the imaging processing unit in a second mode.

Abstract: Methods and systems for active resonant voltage switching are provided. One active resonant switching system includes a voltage switching system having one or more active resonant modules to provide a switching voltage output. Each of the resonant modules includes a plurality of switching devices configured to operate in open and closed states to produce first and second voltage level outputs from a voltage input. The resonant modules also include a capacitor connected to the switching devices and configured to receive a discharge energy during a resonant operating cycle when switching an output voltage from the first voltage level to the second voltage level, wherein the capacitor is further configured to restore system energy when switching from the second to first voltage level. The resonant modules further include a resonant inductor configured to transfer energy to and from the capacitor.

Abstract: A diagnostic device system has a weight-reduced rechargeable battery. When a portable radiographic apparatus and a portable X-ray source are carried to and used for imaging at a private home or a care home, the portable radiographic apparatus and the portable X-ray source are loaded on an automobile. When the charge amount of rechargeable batteries for operation housed in the portable radiographic apparatus or the portable X-ray source loaded on the automobile is low, or when there are plural destinations and the charge amount of the rechargeable batteries becomes low, a rechargeable battery for charging mounted on the automobile is used to charge the rechargeable batteries for operation while traveling. Because the rechargeable batteries for operation are charged while traveling, a large number of rechargeable batteries for operation does not need to be charged in advance, whereby the weight of the rechargeable batteries for operation can be reduced.

Abstract: A method for generating a fast rise-time X-ray pulse includes the steps of providing an n-phase x-ray generator, the x-ray generator including an n-phase transformer having at least one primary winding and at least one secondary winding per phase, and providing n sections of rectifiers, each rectifier having at least a fast pulse rise-time mode and a n-phase ripple flat-top mode. According to the method, at least a first capacitor is charged in each of the n sections of rectifiers at a ripple of less than n-phases to create a fast leading edge of the fast rise-time pulse, and at least a second capacitor is charged in each of the n sections or rectifiers at an n-phase ripple to create a substantially flat-top of the fast rise-time pulse.

Abstract: A portable radiographic imaging device and a portable X-ray source, that operate due to a first and second rechargeable battery respectively, can be accommodated in an accommodating case that is portable. While the accommodating case is being transported, a charging circuit provided in the accommodating case acquires electric power from a third rechargeable battery accommodated in the accommodating case, and charges the first and second rechargeable batteries. In this way, by accommodating the portable radiographic imaging device and the portable X-ray source in the accommodating case, the rechargeable batteries for the portable radiographic imaging device and the portable X-ray source are charged during transport.

Abstract: Among other things, one or more techniques and/or systems are provided for varying a voltage applied to a radiation source of an imaging modality to vary an energy of emitted radiation. A power supply comprises at least two rectifiers, with a first rectifier being electrically separated from a second rectifier via a switching component. When the switching component is opened, the first and second rectifiers are effectively arranged in parallel, and when the switching component is closed, the first and second rectifiers are effectively arranged in series. The voltage applied by the power supply may be different based upon whether the rectifiers are arranged in parallel or in series, but the power output by the power supply may remain substantially constant regardless of the rectifier arrangement.

Abstract: The present invention relates to an X-ray imaging apparatus, and more particularly, to an X-ray imaging apparatus in which a condenser is charged with low battery voltage, and the charged voltage of the condenser, or the sum voltage of the output voltage of the battery serially connected to the condenser and the charged voltage of the condenser is used as X-ray generating power. The X-ray imaging apparatus according to the present invention is configured such that the battery power and the condenser power are serially connected to provide power for operating the X-ray imaging apparatus, thus generating power for operating the X-ray imaging apparatus from the low battery power, and obtaining a lightweight and less bulky X-ray imaging apparatus.

Abstract: The X-ray equipment related to the embodiment is configured from a plurality of pressure rising units, a switching unit, and a switching control unit. The plurality of pressure rising units are connected to the battery unit and generate direct current voltage. The switching unit switches over the plurality of pressure rising units and supplies direct current voltage to the X-ray generating unit. The switching control unit transmits switching instructions to the switching unit for switching over the pressure rising unit after receiving voltage supply instructions with respect to the X-ray generating unit until said voltage supply instructions terminate. The switching control unit controls discharging of the condenser inside the pressure rising unit switched over by the switching instructions and the control of commencing charging of the condenser inside the pressure rising unit following termination of discharging.

Abstract: One or more techniques and/or systems described herein implement, among other things, an energy storage component disposed in a stationary portion (e.g., non-rotating portion) of a CT scanning apparatus. The energy storage component receives electrical power from an external source, such as a power outlet, and stores the electrical power. The stored electrical power is provided for an operation on a rotating portion (e.g., non-stationary) of the CT scanning apparatus upon demand, and is sufficient to perform the operation alone or in combination with power from the external source.

Abstract: An imaging tomography apparatus has electronic components provided to operate the tomography apparatus, with at least one of the electronic components exhibiting a power consumption in high power operation that is significantly increased relative to power consumption in normal operation. The imaging tomography apparatus has an energy storage that, in high power operation, supplies the at least one electronic component with additional electrical energy to cover an energy demand due to the difference in power consumption between normal operation and high power operation. The provision of the additional electrical power in high power operation by means of the energy storage allows the modules that participate in the power supply of the at least one electronic component to be realized with lower cost. Such participating modules can be, for example: the mains connection, junction boxes with power switches (safeguards); a transformer, a rectifier, cables, slip ring brushes, slip ring tracks, etc.

Abstract: A method for generating a fast rise-time X-ray pulse includes the steps of providing an n-phase x-ray generator, the x-ray generator including an n-phase transformer having at least one primary winding and at least one secondary winding per phase, and providing n sections of rectifiers, each rectifier having at least a fast pulse rise-time mode and a n-phase ripple flat-top mode. According to the method, at least a first capacitor is charged in each of the n sections of rectifiers at a ripple of less than n-phases to create a fast leading edge of the fast rise-time pulse, and at least a second capacitor is charged in each of the n sections or rectifiers at an n-phase ripple to create a substantially flat-top of the fast rise-time pulse.

Abstract: An electrical power supply of an X-ray tube. A high voltage generation device having a primary capacitor is configured to transmit a high voltage to the X-ray tube. At least one voltage source is configured to supply the primary capacitor. An energy storage device has an auxiliary capacitor that is configured to receive from the primary capacitor a quantity of energy and to return said energy to the primary capacitor. A control device arranged in series between the high voltage generation device and the storage device is configured to connect or isolate the storage device from the high voltage generation device so the X-ray tube is powered by a variable high voltage very rapidly between a first high voltage and a second high voltage.

Abstract: One or more techniques and/or systems described herein implement, among other things, an energy storage component disposed in a stationary portion (e.g., non-rotating portion) of a CT scanning apparatus. The energy storage component receives electrical power from an external source, such as a power outlet, and stores the electrical power. The stored electrical power is provided for an operation on a rotating portion (e.g., non-stationary) of the CT scanning apparatus upon demand, and is sufficient to perform the operation alone or in combination with power from the external source.

Abstract: The present invention relates to an X-ray imaging apparatus, and more particularly, to an X-ray imaging apparatus in which a condenser is charged with low battery voltage, and the charged voltage of the condenser, or the sum voltage of the output voltage of the battery serially connected to the condenser and the charged voltage of the condenser is used as X-ray generating power. The X-ray imaging apparatus according to the present invention is configured such that the battery power and the condenser power are serially connected to provide power for operating the X-ray imaging apparatus, thus generating power for operating the X-ray imaging apparatus from the low battery power, and obtaining a lightweight and less bulky X-ray imaging apparatus.

Abstract: An X-ray apparatus includes a converter into which there is integrated a control logic circuit configured to regulate the supply voltage of a high-voltage power supply source of the X-ray apparatus. To this end, the intelligent voltage-voltage, converter is placed between the power battery and the capacitor bank. This intelligent converter is capable of determining the optimum voltage to be delivered to the generator for the radiology examination to be undertaken in regulating the current of the power battery at the necessary level of current.

Abstract: An X-ray apparatus includes a converter into which there is integrated a control logic circuit configured to regulate the supply voltage of a high-voltage power supply source of the X-ray apparatus. To this end, the intelligent voltage-voltage, converter is placed between the power battery and the capacitor bank. This intelligent converter is capable of determining the optimum voltage to be delivered to the generator for the radiology examination to be undertaken in regulating the current of the power battery at the necessary level of current.

Abstract: Systems, methods and apparatus are provided through which in some embodiments, a mobile imaging system includes one or more fuel cells. Some embodiments include further electric power sources, such as battery and/or an external AC power source.

Abstract: An X-ray-generator irradiates X-rays at a subject. The X-ray-detector detects the X-rays that have permeated the subject. The rotating body on which the X-ray-generator and the X-ray-detector are installed rotates around the subject. The rotating body is rotated by the drive part. The power source supplies electrical power to the drive part. The step-down part lowers the voltage of the regenerative electrical power generated at the drive part during the deceleration of the rotating body. The accumulation part charges the lowered electrical power. The step-up part raises the voltage of the electrical power from the accumulation part and supplies electrical power to the drive part.

Abstract: An imaging tomography apparatus has electronic components provided to operate the tomography apparatus, with at least one of the electronic components exhibiting a power consumption in high power operation that is significantly increased relative to power consumption in normal operation. The imaging tomography apparatus has an energy storage that, in high power operation, supplies the at least one electronic component with additional electrical energy to cover an energy demand due to the difference in power consumption between normal operation and high power operation. The provision of the additional electrical power in high power operation by means of the energy storage allows the modules that participate in the power supply of the at least one electronic component to be realized with lower cost. Such participating modules can be, for example: the mains connection, junction boxes with power switches (safeguards); a transformer, a rectifier, cables, slip ring brushes, slip ring tracks, etc.

Abstract: The invention relates to an electrical power supply of an X-ray tube comprising: a high voltage generation device configured to transmit a high voltage to the X-ray tube comprising: a primary capacitor; at least one voltage source configured to supply the primary capacitor; an energy storage device comprising: an auxiliary capacitor configured to receive from the primary capacitor a quantity of energy and to return said energy to the primary capacity; a control device arranged between the generation device and the storage device, the generation, storage and control devices being connected in series, the control device being capable of connecting or isolating the storage device from the generation device such that the X-ray tube is powered by a variable high voltage very rapidly between a first high voltage and a second high voltage.

Abstract: Apparatus includes a fixed computed tomography (CT) system including a storage device configured to share power delivery with an input power line in order to reduce peak load requirements of the input power line.

Abstract: In one embodiment, a voltage rectifier circuit for a radiation generator is provided. The voltage rectifier circuit is configured to be used in a voltage multiplier circuit and a voltage doubler circuit. The voltage rectifier circuit comprises at least one first printed circuit board and at least one second printed circuit board coupled to each other using a plurality of connectors. Further, each printed circuit board comprises, a first terminal, a second terminal, a third terminal, a diode assembly externally connected between the first terminal and the second terminal and a capacitor assembly embedded between the second terminal and the third terminal.

Abstract: An X-ray CT apparatus according to this invention comprises X-ray generating unit which irradiates X rays toward a object, detecting unit which detects X rays irradiated from the X-ray generating unit and passed through the object, support unit which supports the X-ray generating unit and the detecting unit, driving unit which rotates the support unit, and control unit which controls the driving unit, accumulates regenerative energy generated when the rotating speed of the support unit is decelerated, and supplies the accumulated regenerative energy to the driving unit to rotate the support unit.

Abstract: A voltage generator for an X-ray machine comprising an X-ray tube with a cathode and an anode is described. The voltage generator comprises a negative voltage multiplier for supplying a polarisation voltage to the X-ray tube and a filament transformer which can be connected to the X-ray tube for supplying an energisation voltage to the X-ray tube. The voltage generator is characterized in that the negative voltage multiplier comprises a cavity able to house said filament transformer.

Abstract: A semiconductor switch 12 connected in series with a smoothing capacitor 12 is constituted by connecting in parallel a diode 13D which permits to flow current regenerated from energy of electric charges stored in a high voltage capacitor 17 to a primary side of a high voltage transformer 15 for the smoothing capacitor 12 and switching means 13S which interrupts an output from the smoothing capacitor 12, and after turning off the switching means 13S, through alternative on and off control of switching means 161S˜164S the energy of electric charges stored in the high voltage capacitor 17 is regenerated to the smoothing capacitor 12 by making use of parasitic leakage inductance 15L. As a result, an X-ray high voltage device is provided which permits to drop a wave tail of a tube voltage in a high speed without complexing the structure of the high voltage part thereof.

Abstract: A light generation apparatus is capable of widely changing the intensity of generated light. The light generation apparatus includes an X-ray source, a high-voltage generation circuit, and a CPU. The high-voltage generation circuit has a plurality of capacitors, and a plurality of switches, which are arranged on the charging and discharging paths of the capacitors. The CPU controls the switches to switch a capacitor for supplying electric energy to the X-ray point source, thereby changing electric energy supplied to the X-ray point source.

Abstract: The voltage applied to a first grid electrode 71 of an X-ray tube 11 by a grid voltage control section 110 is controlled with reference to a predetermined negative voltage from a negative voltage generating section 112 when an object 5 to be inspected does not exist in an imaging area (irradiation area of an X-ray from an X-ray source 1) so that the pulse outputted from a pulse generator 105 is in its OFF state, and is controlled with reference to a reference positive voltage from a reference voltage generating section 115 when the object 5 to be inspected exists in the imaging area in the X-ray image intensifier 2 (irradiation area of the X-ray from the X-ray source 1) so that the pulse outputted from the pulse generator 105 is in its ON state, whereby both of the cutoff voltage and grid operating voltage are applied in a stable state.

Abstract: An X-ray examination apparatus is provided with a DC voltage source which is to be connected to a maines voltage and whereto there are connected an accumulator with a charging circuit for this the accumulator as well as a high voltage generator for an X-ray tube. The accumulator is charge in a standby mode; the accumulator can be discharged via the high voltage generator. There is provided a power gate circuit via which power up to a maximum value can be drawn from the mains, the accumulator being chargeable for as long as this maximum value has not yet been reached; when a power beyond said maximum value is required, the surplus beyond this maximum value is delivered by the accumulator via said power gate circuit.

Abstract: A portable x-ray system includes an x-ray source, an internal power supply for supplying an input voltage, and a voltage converter in electrical connection between the power supply and the source. The converter varies the input voltage from the power supply to provide an output voltage useable in the x-ray source to generate x-rays of a predetermined energy. The power supply includes a battery power store, a capacitor power store, and a switching unit to selectively connect the power stores to the voltage converter individually or together to provide the input voltage to the voltage converter during an exposure.

Abstract: An apparatus for energizing a large scale medical imaging system, preferably in the form of a CT scanner so that the scanner operates off an uninterruptable power supply in the event that the external power falls below sufficient power to operate the system so that system operation remains uninterruptable. The system is designed to operate off a broad range and types of external power supplies including those providing DC, single or three phase AC power. The system therefore can operate from a common single phase AC outlet. In addition, power factor correction is provided so that the system can correct for phase differences between the voltage and current at the input line created by the input impedance of the system.

Abstract: In a CT (computerized tomographic) scanning apparatus, a biological body under medical examination is scanned to acquire image data on the scanned body, whereby a computerized tomographic image of the scanned body is reconstructed by processing the acquired image data. The CT scanning apparatus comprises: an AC/DC converting unit for converting AC (alternating current) power supplied from a commercial power source into first DC (direct current) power; a peak power consumption unit for consuming peak power during a scanning operation; and a secondary battery unit rechargeable by the first DC power supplied from the AC/DC converting unit and capable of supplying second DC power to the peak power consumption unit during at least the scanning operation.

Abstract: A high-frequency x-ray generator having low high-voltage ripple at the x-ray tube with a small amount stored energy in the high-voltage circuit and low drive frequency has a series of secondary windings each connected to a high-voltage rectifier having a capacitor connected in parallel. These capacitors are connected in series for forming the x-ray tube voltage. Each secondary winding has a primary winding allocated to it. The primary windings in combination with delay capacitors form a delay line in which a traveling wave is generated by a primary voltage source.

Abstract: A small, hand held X-ray machine is constructed to be readily portable, including a portable power supply, yet is sufficiently powerful to take an X-ray of a human patient. The X-ray machine includes a ceramic X-ray tube which is resistant to shocks and vibrations, structurally strong, as well as light weight, further contributing to the convenient portability of the X-ray machine.

Abstract: A pulsed precision x-ray source includes a miniaturized internally self-shielding x-ray tube and an integral generator contained in a hand-held housing for generating timed bursts of x-ray having regulated energy level. A control grid and focus electrode within the tube enable precise on-off control of an electron beam directed to an x-ray emitting anode. The integral generator system includes an elongated, U-shaped unitary, molded plastic block mounted in the housing and includes a high voltage transformer having primary and secondary annular windings encased in a transformer portion of the block defining a central opening outside of the block for receiving a transformer core therethrough and, a capacitor-diode voltage multiplier stack connected to the secondary winding and having a positive node connectable to the anode and a negative node connectable to the cathode.

Abstract: An exposure control (A) selectively applies electrical power across a transformer (10) of a high voltage power supply (B). The high voltage power supply boosts the voltage such that an output voltage on the order of 150 kV is provided on output lines (20+, 20-). The output lines, typically long cables, are connected with a high voltage device such as an x-ray tube (C) to control the generation of a beam of x-rays (D). Due to high internal capacitance (22, 28) of the power supply, the cables, and the x-ray tube, the output lines continue to carry a potential (34) after the end t.sub.2 of the selected duration. At the end of the selected duration, a pulser (62, 80) applies an electrical energy pulse which causes a medium in a gap (56, 76) between electrodes (52, 54; 72, 74) to be ionized. Once the medium is ionized, the stored electrical energy arcs through the ionized medium and flows quickly to ground as indicated at (42).

Abstract: A mobile X-ray machine utilizes batteries to provide electrical power to produce high-voltage necessary to generate X-rays during a X-ray exposure. A battery charger circuit is used to supplement the battery during the X-ray exposure and charges the batteries during non-exposure periods. By using batteries to power the X-ray generating device, the X-ray machine is capable of being operated from 110 volt AC power sources permitting the machine to be mobile due to its ability of being operated from ordinary house current.

Abstract: A single tank X-ray diagnostic generator has a double focus X-ray tube, two high voltage transformers feeding the X-ray tube, and two doubler circuits respectively connected to the secondaries of the high voltage transformers for doubling the output voltage thereof, each doubler circuit consisting of two high voltage rectifiers and two high voltage capacitors. All of the components are contained in a single oil-filled receptacle having a radiation exit window through which the X-rays are emitted. The transformers for supplying the filament voltages to the X-ray tube filaments are adjacently disposed in the receptacle at one end of the X-ray tube.

Abstract: A mobile X-ray apparatus (20) is disclosed which incorporates a power supply (22) in which the energy for operation of the X-ray tube (21) is supplied from a flywheel (50) coupled to an electrical machine (24) which functions as both a motor and generator. In the motor mode of operation, a controller (21) provides power to the machine (24) to operate it as a motor and drive the flywheel up to a desired operating speed. Upon request of the operator to initiate an exposure, the controller power is disconnected from the machine and the power terminals (32) of the machine (24) are connected to a transformer and rectifier (27) which increases the generated voltage and rectifies it to provide the high voltage across the X-ray tube (21) required for proper exposures.

Abstract: Stability of the optical path in a laser resonator cavity is achieved by means of two reflective surfaces mounted orthogonally with respect to each other, serving as the reflector at one end of the resonator cavity. Return and feedback mirrors are rigidly mounted at the opposite end of the aforementioned resonator cavity. Changes in relative orientation not self-compensated by the use of orthogonally-mounted mirrors are corrected by means of a real-time servomechanism. A typical servomechanism comprises an auxiliary laser mounted rigidly to one end of the laser resonator cavity reflecting a collimated light beam from a reflector mounted rigidly to the opposite end of the resonator cavity. The reflected spot is detected by a detector, sensitive to positional changes in the reflected light, rigidly mounted with respect to the auxiliary laser. The positional changes of this reflected spot are used to drive a linear translator to correct the relative orientation in real-time.

Abstract: In an exemplary embodiment, the secondary parts of the high voltage transformers each are connected with a respective doubler circuit formed of rectifiers and capacitors. All components are arranged in a single oil-filled receptacle which has a radiation exit window for transmitting the x-radiation. The two high voltage transformers are disposed symmetrically relative to the radiation exit window in proximity to respective receptacle sidewalls and adjacent the x-ray tube. The rectifiers and capacitors are disposed above the x-ray tube and symmetrically relative to the radiation exit window.

Abstract: In an exemplary embodiment, with a high voltage rectifier, two individual capacitors connected in series across the rectifier output, and radiation shielding surrounding the x-ray tube, the radiation shielding is connected with the connection line of the two individual capacitors in an electrically ungrounded fashion and the cathode of the x-ray tube is connected to ground.

Abstract: A mobile X-ray machine utilizes batteries to provide electrical power to produce high-voltage necessary to generate X-rays during a X-ray exposure. A battery charger circuit is used to supplement the battery during the X-ray exposure and charges the batteries during non-exposure periods. By using batteries to power the X-ray generating device, the X-ray machine is capable of being operated from 110 volt AC power sources permitting the machine to be mobile due to its ability of being operated from ordinary house current.