CN105992446B - X-ray imaging device and the method being imaged for x-ray - Google Patents
X-ray imaging device and the method being imaged for x-ray Download PDFInfo
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- CN105992446B CN105992446B CN201510059102.5A CN201510059102A CN105992446B CN 105992446 B CN105992446 B CN 105992446B CN 201510059102 A CN201510059102 A CN 201510059102A CN 105992446 B CN105992446 B CN 105992446B
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Abstract
The present invention provides x-ray imaging device.X-ray imaging device receives electric power from high-voltage generator.X-ray tube emits ionizing radiation when the voltage generator is switched on, and the ionizing radiation is cut off when the voltage generator is disconnected.Discharge cell is electrically connected to the x-ray tube, and promptly discharges it when the high-voltage generator is disconnected.Method for x-ray imaging is also provided.
Description
Invention field
The present invention relates to the fields of radiographic, and in particular it relates to for reducing from x-ray voltage generator
The device and method of the fall time of the high voltage of output.
Background technique
The transmitting of x-ray may be required to provide high voltage according to system(Such as more than the output voltage of 100 kV)'s
Power supply.The generation and control of such high voltage need special equipment and force many requirements to X-ray system design, including
With personal security, heat dissipation, device housings design and installation and to the related requirement of the electromagnetic interference of other equipment.Because institute
One consideration of the energy level of realization, the user of these systems is related to the efficient management of imaging device, is included in imaging completion
After terminate radiation-emitting.
The challenge of the designer of x-ray camera installation is faced in order to better understand energy management and control considers x
Ray system how to be powered with emit radiation and system can how may be by control during and after imaging cycle
Beneficial.For example, the signal of Fig. 1 is shown for object 12(Such as tooth patient)The x-ray device 10 being imaged
Component.Generator 20 be it is drivable, be provided across x-ray tube 30 high voltage output 22.Additional low-voltage output
24 provide the heating to the filament 34 of x-ray tube 30, filament 34 and then heating cathode 32.Variable auto-transformer 26 is via high electricity
Pressure booster 21 is connected to high-voltage output terminal 22.It can be controlled via variable operation person's control 28 and/or variable resistance 29
Variable transformer 26 enables to the high voltage output 22 of the type of imaging needed for adjustment is suitable for object 12.Reducing transformer
23 are connected to power switch 15, and are connected to the filament 34 of x-ray tube 30 and are added with providing when switch 15 is switched on for it
Thermocurrent.Visual detector 40(It is also known as picture receiver)It is obtained as caused by the x-ray 11 emitted from x-ray tube 30
Picture material.In the embodiment illustrated, detector 40 can be the tooth piece being temporarily retained in the mouth of tooth patient.?
In alternative embodiment, for example, detector 40 can be film magazine or digital imagery receiver(DR).
The signal of Fig. 2 shows the component of x-ray tube 30.The high-voltage output terminal 22 of generator 20 from Fig. 1 is horizontal
It is electrically connected across anode 36 and cathode 32.From the cathode 32 that filament 34 heats to 36 flow of emitted electrons 35 of anode.Electron stream 35 is horizontal
It advances across the gap formed and making the anode 36 and cathode 32 spaced apart in x-ray tube 30.This high-energy electron stream is hit
Often target 38 made of tungsten are got through, but the target 38 is alternatively made of molybdenum, suitable alloy or other high refractory metals.Target 38
Transmitting can be pointed to the ionizing radiation 43 of object 12.X-ray tube 30 is typically encased in outside the lead of x-ray for stopping transmitting
In shell 42, but x-ray tube 30 could be formed with window 44, and window 44 allows x-ray 43 in the desired direction from x-ray tube 30
Transmitting.For cooling purpose, x-ray tube 30 can be oil-filled.
It is trained to follow limitation patient to the convention of the exposure of radiation using the imaging technologist of radiographic apparatus,
Wherein, the radiation is more unlike radiation needed for obtaining suitable radiographic images.The factor that can be controlled can be with
It is the time interval during x-ray tube 30 emits radiation, x-ray.Exposure cycles can be in the sufficient radiation for imaging by x-ray
Source emits and is terminated after receiving at detector.However, may be taken some time using high-voltage part to reduce
Energy at x-ray tube 30, to cut off its x-ray emission.As shown in Figure 3, x-ray tube voltage curve Figure 60 is illustrated such as
The typical timing of x-ray emission starting and termination in imaging device disclosed herein.It can be at time t0 using switch 15
Connect the high voltage that x-ray tube 30 is applied to from voltage generator 20.The rise time of generated voltage can reach sufficient water
It is flat, at about the 75% of maximum horizontal, to realize x-ray exposure at time t1.When with 15 off voltage generator of switch
When, the exposure of object 12 can be completed at time t2.However, the fall time of the voltage applied may be it is appreciable,
So that it is more than turn-off time t2 to time t3 that the Net long wave radiation exposure of object 12, which extends,.Difference(t3 - t2)It can be shown as compensating
Time t'.Radioactive exposure effectively occurs until time t3, and in time t3, the voltage applied has dropped to maximum voltage
About 75% or less.As a result, object 12 may be from time t1 to time t3 rather than as required from time t1 to time t2
Interim be exposed.Compared with needs, this may be by extended led from the fall time of maximal voltage level
The long radioactive exposure duration caused.The exposure that picture contrast may also be extended adversely affects.This when
Between delay force the constraints of various types of applications, such as pulse perspective and its using the multiple images by rapid sequential shooting
Its imaging pattern.
In general, total irradiation time can be measured as to the time interval between t1 and t3.Time t1 indicates from high voltage
The output voltage of generator to x-ray tube has realized the 75% of peak value and the x-ray emitted is for the imaging of effective x-ray
The sufficient time.Time t3 indicates that the output voltage to x-ray tube drops to the 75% of peak value and the x-ray emitted is had
Imitate the time of cutting.
Area and international standard(Such as international standard IEC60601-2-7)For the high voltage in diagnosis x-ray generator
The safety of generator provides particular requirement, the duration including irradiation time.As mentioned above with reference to fig. 3, practical spoke
It can be the time interval between t1 and t3 according to the time, even if high-voltage generator can disconnect at time t2.Institute is extended
Interval between fall time, especially time t2 and time t3 influences exposure both criterion and imaging characteristic.In t2 and t3
Between this interim transmitting x-ray be sometimes referred to as " soft " x-ray, and have may be too low to be used for
Imaging still increases the energy level of the dose of radiation of patient.In addition, they are added to excess current to the thermic load of x-ray tube,
This reduces the service life of pipe.
The factor of the fall time of x-ray tube voltage 60 shown in influence diagram 3 is prolonged from high-voltage generator 20
Reach the natural capacity in the cable of x-ray tube 30.The length of these cables can be from about 9 meters to about 26 meter(m)It changes,
Wherein physical length depends on used particular device.Cable may include braiding copper signal shielded layer or sheath.By electricity
The natural capacity for the cable that cable conductor and shielded layer are formed is proportional to cable length.The representative value of the capacitor can be about
145 pF/m(Every meter of pico farad).For example, having used two 26m cables(One be used to will be each in anode 36 and cathode 32
It is a to be connected to voltage generator 20, wherein shielding layer grounding)In the case where, the capacitor between anode 36 and ground can be about
3770 pF.Same capacitor is present between cathode 32 and ground.It is positive because anode and cathode is electrically connected in a series arrangement
Total equivalent capacity of cable between pole and cathode can be about 1885 pF.This may electrically be equivalent to large capacitor
Arrangement in circuit, and has a significant effect to the switch response characteristic of the output voltage 22 from generator 20.Therefore, when disconnected
Open voltage generator export when, actual output voltage is decayed over time, as shown in Figure 3, wherein signal can
It is as illustrated to discover " tail portion ".Effective transmitting of x-ray deadline t2 and 75% power level at time t3 it
Between continue.Due to the voltage decay time, subject patient may be exposed to additional radiation during compensating time interval t'
Dosage.Further, since additional exposure, the accuracy of data or other calculating based on output voltage may be affected.
It can be in exposure software algorithm for exposure duration accuracy to be maintained a strategy in standard requirements
Break time t2 is effectively moved on to earlier time hence for exposure under automatic control by compensated in advance cable capacitance.With
This mode, the cutting of software control shorten conduction time to realize desired exposure.However, this method may be not
Accurately and may at some restricted exposure parameters hazardous voltages signal accuracy.Moreover, this method is for making
It can effectively be worked with the system of software control, the case where this may not be all X-ray systems.
It always strives to reduce the method for fall time to be using " extinguishing arc(crow-bar)" circuit.Crowbar circuit is literal
On make the output short-circuit of x-ray generator at desired break time, to more quickly make associated with x-ray generator
Output capacitance(Natural capacity including the cable from x-ray generator to x-ray tube)Electric discharge.Crowbar circuit can be efficiency
Low, because they fall the energy of storage as heat waster, and having for some x-ray generator electronic components may be reduced
With the service life, because peak transition associated with the operation of crowbar circuit may be brokenly for the component in high current path
Bad property.Accordingly, it can be seen that in the presence of the high voltage for being used to more quickly reduce the characteristic as conventional x-ray generator
The needs of the device and method of fall time.
Summary of the invention
The purpose of the disclosure is to promote the technology of radiographic.Advantageously, embodiment of the disclosure provides side
Help the solution for shortening the fall time of the high voltage in radiographic application.These purposes only pass through illustrated examples
It provides, and such purpose can be the demonstrative example of one or more embodiments of the invention.By of the invention intrinsic
Ground realize other desired objects and advantage can be expected by those skilled in the art or for this field technology
It is become apparent for personnel.
According to one aspect of the disclosure, the x-ray imaging device including voltage generator is provided, the voltage occurs
Device may be switched to connect when generator is switched on across the x-ray anode of x-ray source and the activation voltage of x-ray cathode, and
And it may be switched to disconnect the activation voltage when the activation voltage is disconnected.The x-ray source is configured as swashing described
Voltage living emits ionizing radiation when being switched on, and is configured to cut off the ionizing spoke when the activation voltage is disconnected
The transmitting penetrated.Discharge cell is electrically connected to x-ray source and including being used for the sun when the activation voltage is disconnected
The discharge circuit that pole is electrically connected to the cathode to discharge the activation voltage.
According to another aspect of the present disclosure, x-ray imaging device is provided comprising have and be configured to make voltage generator
The voltage generator of the switch switched on and off.X-ray tube is electrically connected to the voltage generator, and sends out in the voltage
Raw device emits ionizing radiation when being switched on, and the ionizing radiation is cut off when the voltage generator is disconnected.Electricity
It includes in the voltage generator quilt that property, which is connected to the x-ray tube and is electrically connected to the discharge cell of the switch,
The anode is electrically connected to the discharge circuit of the cathode when disconnection.
According to another aspect of the present disclosure, the method for x-ray imaging, including activation voltage generator, packet are provided
It includes and is provided across the high voltage of x-ray tube from the voltage generator and ionizing radiation is emitted by the x-ray tube.
Discharge circuit is electrically connected to the voltage generator in a manner of in parallel with the x-ray tube, and occurs in the voltage
Across the short-circuit x-ray anode of the discharge circuit and the x-ray when device is disconnected and the discharge circuit is powered
Cathode.
This brief description of the invention is meant only to provide public according to this paper institute of one or more illustrative embodimentss
The brief overview for the theme opened, and be not used as explaining claim or define or limit the guidance of the scope of the present invention, this
The range of invention is defined solely by the appended claims.This brief description is provided to introduce in simplified form hereafter detailed
The illustrative selection of the design further described in thin description.This brief description is not intended to the pass for identifying advocated theme
Key feature or essential feature, it is also not intended to be used as help in determining the scope of the claimed subject matter.Advocated
Theme is not limited to any or imperfect realization of institute for solving to be previously mentioned in the background technology.
For example, above summary description is not intended to describe its element to be non-swappable individual individual embodiments.It is practical
On, being described as many elements related with specific embodiment can be used together with the element of the embodiment of other descriptions,
And it may can be exchanged with the element of the embodiment of other descriptions.It without departing from the spirit of the invention, can be in this hair
Many changes and modifications are made in bright range, and the present invention includes all such modifications.Following attached drawing is intended to neither
Any precise proportions are plotted as relative to relative size, angular relationship, relative position or timing relationship, also not relative to needs
The expression of embodiment, interchangeability or substitution be plotted as any combination of relationship.
Detailed description of the invention
This hair may be described in detail in such a way that feature of the invention is understood that by referring to specific embodiments
Bright, some in specific embodiment are illustrated in the accompanying drawings.It should be noted, however, that attached drawing illustrates only specific reality of the invention
It applies example and is therefore not to be regarded as limiting its range, because the scope of the present invention includes other equivalent effective embodiments.It is attached
Figure is not drawn necessarily to scale, and emphasis is generally placed in the feature of the specific embodiment illustrated the present invention.In attached drawing
In, same appended drawing reference is used to refer to same part in all various views.Therefore, for a further understanding of this hair
It is bright, can refer to it is described in detail below read together with attached drawing, in attached drawing:
Fig. 1 shows the schematic diagram of the x-ray imaging device with x-ray generator according to the prior art;
Fig. 2 shows the schematic diagrames of the x-ray tube according to the prior art;
Fig. 3 is the curve of the x-ray starting and the voltage waveform terminated in the imaging device shown according to the prior art
Figure;
Fig. 4 is to show the schematic diagram of the x-ray device according to an embodiment of the present disclosure using discharge cell;
Fig. 5 is to show the improved electricity of x-ray starting and termination in imaging device according to an embodiment of the present disclosure
The curve graph of corrugating;
Fig. 6 is to show the timing diagram of control and electric power signal timing according to an embodiment of the present disclosure;And
Fig. 7 to Fig. 8 is to show the signal of the x-ray device using discharge cell of the alternate embodiment according to the disclosure
Figure.
Specific embodiment
It is hereafter with reference to attached drawing detailed description of the preferred embodiment, wherein identical in each of several attached drawings
The similar elements of appended drawing reference mark structure.Using its, unless otherwise stated, otherwise term " first ", " the
Two " etc. not necessarily indicate any order, sequence or priority relationship, and are used only to more clearly make an element or one group
Element is distinguished with other elements or other set of pieces.As it is used herein, term " can be to electricity " is related to receiving electricity
The equipment or a group parts of indicated function when power and are optionally executed when receiving enable signal.For example, term " can
Driving " with its conventional meaning, being related to perhaps can be in response to stimulation(Such as in response to electric signal)And what realization acted sets
Standby or component.In the context of the disclosure, term " operator ", " technical staff " and " user " be considered as it is equivalent,
Refer to the personnel of operation x-ray imaging device.In the context of the disclosure, term " non-irradiation " is referred to when being powered not
Transmitting can measure or can perceive the component of the ionizing radiation of quantity.Phrase as used in this disclosure is " with signal communication
Mode " instruction electric connection, two or more equipment and/or component can be shared in certain type of by the electric connection
The one or more signals advanced on signal path.Signal communication can be wired or wireless.Signal can be can edge
Signal path between the first equipment and/or component and the second equipment and/or component by information, electric power, and/or energy from
One equipment and/or component are transmitted to communication, electric power, data or the energy signal of the second equipment and/or component.Signal path can be with
Including between the first equipment and/or component and the second equipment and/or component physics, electrical, magnetic, electromagnetism, optics, it is wired and/
Or it is wirelessly connected.Signal path can also include that additional between the first equipment and/or component and the second equipment and/or component sets
Standby and/or component.
Fig. 4 is to show showing including the x-ray imaging device 10 above with respect to high-voltage generator 20 described in Fig. 1
It is intended to, wherein for purposes of clarity, some element identifiers are not shown in figure.Discharge cell 50 can be with voltage generator 20
It is spaced apart and is electrically connected to it, may be the high voltage fall time of the characteristic of conventional x-ray tube 30 to reduce.Discharge cell
50 are electrically connected across the high voltage output 22 from x-ray generator 20.X-ray generator 20 can be it is drivable, thus
The high voltage of x-ray tube is provided across by output 22.Discharge cell 50 can be electrically connected to by conductor wire 22a and 22b
High voltage output 22.Discharge cell 50 can with right and wrong irradiate and can have vacuum discharge tube 54, the vacuum discharge tube
54 may be slightly similar with x-ray tube 30 in terms of its electric loading characteristic.That is, exporting 22 institutes relative to by high voltage
The electric current of offer, vacuum discharge tube 54 is configured as that electrical characteristic identical with x-ray tube 30 is presented, but does not generate measurable water
Flat x-ray or other ionizing radiations.Vacuum discharge tube 54 can be configured as not for emitting the target of radiation(For example,
The 38 of Fig. 2).The discharge tube 54 of discharge cell 50 is electrically connected to x-ray tube 30 with parallel way.When x-ray tube 30 is operating
In when being activity, discharge cell 50 can be disabled and make discharge tube 54 that the high impedance of cross span 22a and line 22b be presented and do not have
Appreciable electric current flows into discharge cell 50 by there.Therefore, discharge cell 50 is during x-ray exposure to x-ray tube 30
Driving voltage there is no influence.
When the exposure for the object being imaged is completed, x-ray tube 30 can be closed by disconnecting power switch 15.In order to
The voltage of x-ray tube 30 is promptly reduced when closed, and discharge signal 46 is when power switch 15 is disconnected by from power switch
15 are sent to the charge/discharge control circuit 48 in discharge cell 50.Discharge signal 46 is activated to adjacent with the cathode 52 in discharge tube 54
Filament 55 to electricity charge/discharge control circuit 48.In response, discharge tube 54 is connected and via electric discharge tube cathode 52 and discharge tube
Remaining high voltage is transmitted to x-ray tube anode 36 from the cathode 32 of x-ray tube 30 by gap of the anode 56 in discharge tube 54.
By discharge tube 54, this effectively makes line 22a to line 22b short circuit, and makes x-ray tube anode 36 to 32 short circuit of x-ray tube cathode
And promptly make across the high voltage decline of x-ray tube 30 to accelerate fall time and cut off as described herein " soft " rapidly
The transmitting of x-ray.Electric discharge across the high voltage of x-ray tube 30 includes by via by voltage generator as described herein
20 are connected to the capacitor stored charge of the cable of x-ray tube 30 and the electric current that generates.For example, discharge signal 46 can substitute
Ground is provided by the operator of x-ray device 10, or can be indicated by the measurement that device 10 is completed in response to exposure(Such as make
With automatic exposure control circuit)To provide.Advantageously, discharge cell 50 allows the repetition of x-ray tube 30 as described herein
Activation and deactivation, such as fluoroscopic image or computed tomography.
Discharge tube 54 be can be used or be packed into for cooling insulating oil.For example, it may include for oil coolant
Oil-filled compartment(It is not shown), those of offer in x-ray tube 30 is provided.Discharge tube 54 can produce light
And/or heat, but be configured as avoiding the generation of ionizing radiation.Discharge tube 54 can remove the target 38 of such as x-ray tube 30
Target or discharge tube 54 the non-tungsten target material 58 of the non-refractory metal for not emitting radiation, x-ray such as can be used.In addition,
The beam of any generation in discharge tube 54 has broader focus compared with can be as provided by x-ray tube 30.This is into one
Step prevents the extra generation of ionizing radiation.However, simultaneously, vacuum discharge tube 54 is presented with the impedance with x-ray tube 30
The electric loading of the impedance and load characteristic similar with load characteristic.
Electric discharge tube anode 56 can be fixed anode or rotary anode.The rotation of electric discharge tube anode 56 is helped in discharge tube 54
Interior distribution heat.Can be separately packaged and install discharge cell 50, allow it be spaced apart with x-ray generator 20 or it
It can be integrated with x-ray generator 20.Advantageously, discharge cell 50 allow x-ray tube 30 repetition drive, such as with
In fluoroscopic image or computed tomography.
Fig. 5 shows the voltage curve similar with voltage curve shown in Fig. 3, and with the voltage curve of Fig. 3 60(It is empty
Line)It compares, illustrates the reduction fall time 70 using discharge cell 50.Here, indicate exposure cycles effectively terminate when
Between t3' faster occur than the time t3 under regular situation shown in fig. 3 after timet.Under the typical case of high voltage signal
Time from a few tens of milliseconds drops(Such as by being equivalent to(t3 - t2)Fig. 3 in time interval t' indicated by)Several milliseconds are changed into,
Such as by being equivalent to(t3' - t2)Fig. 5 in reduction time interval t'' shown in.
Fig. 6 illustrates the timing of the timing relationship between control signal and electric power signal according to an embodiment of the present disclosure
Figure.Driving signal 62 shows the power switch 15 for driving x-ray exposure(Fig. 4)ON/OFF state.It can be in the time
Switch 15 is connected at t0.In response, x-ray generation starts at time t1, as shown in voltage waveform 70.It can be in the time
Switch 15 is disconnected at t2.Discharge signal 46 can be sent at time t2, to make discharge tube 54(Fig. 4)As by electric discharge tube voltage 64
It is powered as shown.X-ray emission is as as shown by voltage waveform 70 and as above with reference to described in Fig. 5
Terminate at time t3' like that.Discharge tube 54 can be completely discharged at time t4.
Using timing shown in Fig. 6, interval t' is used as from such as Fig. 3 in the additional exposure during time interval t''
Shown in significantly reduce.It should be noted that the complete electric discharge of x-ray tube 30 may not be needs in each application.For example,
Before next driving of power switch 15, it may be sufficient to allow the partial discharge of x-ray tube 30.This is only in the exposure duration
Small compromise in the case of, can allow for for x-ray tube 30 faster switch response.
Fig. 7 is to show to have such as the x-ray imaging device 10 above with respect to high-voltage generator 20 described in Fig. 1
Schematic diagram, some of element numbers are not shown in figure for purposes of clarity.Discharge cell 80 is according to alternative embodiment electricity
Property be connected to its with reduce may for conventional x-ray tube 30 characteristic high voltage fall time.Fig. 8, which is illustrated in more detail, to be put
The circuit connection of electric unit 80.With reference to Fig. 7 and Fig. 8, discharge cell 80 is electrically connected across the high voltage from x-ray generator 20
Output 22.X-ray generator 20 may is that it is drivable, thus the high voltages for being provided across x-ray tube by output 22.Electric discharge
Unit 80 can be electrically connected to high voltage output 22 by conductor wire 22a and 22b.Discharge cell 80 may include two or more
Multiple oil-filled chambers.In the embodiment of illustrated Fig. 7, chamber 82a-82c is connected in series to.In other embodiments,
Discharge cell 80 may include two or more parallel branches and each branch includes what two or more were connected in series
Chamber.Fig. 8, which illustrates discharge cell, can be optionally designed as including more than three oil-filled chamber 82a-82e.In Fig. 7 and Fig. 8
Shown in embodiment, chamber 82a-82c and chamber 82a-82e are filled with the independent sphere of insulating oil.Sphere can be by making
The structure of discharge cell 80 is attached to non-conductive insulation strip 85 and is supported.Although the shape with sphere is shown,
It is chamber 82a-c and chamber 82a-e may include other shapes.The chamber and oil of other suitable types can also be provided, including had more
The single oily channel of a hollow cavity.Sphere itself(Or other shapes)It can be made of copper, metal alloy or other conductive materials.
As shown in Figure 8, each of the multiple chamber 82a-e includes small―gap suture.When gap by control of discharge 48 in response to being passed
The high voltage pulse that send and when in breakdown situation, corresponding chamber work in the form of the electric conductor of discharge current described herein
Make.When gap is not at breakdown situation, respective chamber is with dielectric(Insulator)Form work.By using multiple chamber 82a-
C or chamber 82a-e, it is therefore prevented that air breakdown, because can be in chamber 82a-c or chamber 82a-e(More specifically, filled in chamber
In oil)High voltage between common lines 22a and line 22b.
During x-ray exposure, discharge signal 46 is not enabled and does not provide high voltage arteries and veins to chamber 82a-c or chamber 82a-e
Punching, therefore, chamber and line 22a and line 22b disconnect and flow into discharge cell 80 without appreciable electric current.Chamber 82a-c and chamber
The high impedance of cross span 22a and line 22b caused by 82a-e is presented due to insulating oil.Discharge cell 80 is during x-ray exposure
Influence there is no on the driving voltage of x-ray tube 30.
When the exposure for the object being imaged is completed, x-ray tube 30 can be closed by disconnecting power switch 15.In order to
The voltage of x-ray tube 30 is promptly reduced when closed, and discharge signal 46 is when power switch 15 is disconnected, by from power switch
15 are sent to the charge/discharge control circuit 48 in discharge cell 80.The activation of discharge signal 46 can be with the chamber 82a-c and chamber 82a-e that connects
Each of carry out signal communication charge/discharge control circuit 48.In response to receiving discharge signal 46, charge/discharge control circuit 48
Then the high-voltage electricity breakdown pulse of several kV is supplied to each oil-filled chamber 82a-c or chamber 82a-e.Since the conductive characteristic of sphere is high
Voltage breakdown pulse is enough between online 22a and line 22b to cause instantaneously to conduct by each of oil-filled chamber.This makes line in turn
22a makes x-ray tube anode 36 to 32 short circuit of x-ray tube cathode to line 22b short circuit, and by oil-filled chamber, and promptly makes
Across the high voltage decline of x-ray tube 30 to accelerate fall time and quickly shut off " soft " x-ray as described herein
Transmitting.High-voltage discharge by oil-filled chamber 82a-c and chamber 82a-e includes by via as described herein sending out voltage
Raw device 20 is connected to the capacitor stored charge of the cable of x-ray tube 30 and the electric current that generates.For example, discharge signal 46 can
It is alternatively provided, or can be indicated by the measurement that device 10 is completed in response to exposure by the operator of x-ray device 10(It is all
Such as using automatic exposure control circuit)To provide.Advantageously, discharge cell 80 allows x-ray tube 30 as described herein
Reconditioning and deactivation, such as fluoroscopic image or computed tomography.It can be separately packaged and install electric discharge
Unit 80 allows it to be spaced apart or can be integrated with x-ray generator 20 with x-ray generator 20.It is oil-filled
Insulating oil in chamber 82a-c and oil-filled chamber 82a-e may include the suitable insulating oil of any quantity type, including but not limited to
Mineral oil, nano-fluid oil, four fatty acid pentaerythritol esters and natural synthesizing ester, silicon substrate or fluorination hydro carbons are other suitable
Oil.The breakdown pulse being provided can be adjusted according to the oil type that can be used.
It is similar with timing relationship described in the embodiment of discharge cell 50 above with reference to shown in Fig. 4, the electric discharge of Fig. 7
The embodiment of unit 80 is similar to shown in the timing diagram of Fig. 6.Driving signal 62 shows the electricity for driving x-ray exposure
Source switch 15(Fig. 4)ON/OFF state.Switch 15 can be connected at time t0.In response, start at time t1
X-ray generates, as shown in voltage waveform 70.Switch 15 can be disconnected at time t2.As described earlier, may be used
With at time t2 send discharge signal 46, thus make charge/discharge control circuit 48 will puncture pulse 64 be output to it is every in oil-filled chamber
One.X-ray emission as as shown by voltage waveform 70 and as above with reference to described in Fig. 5 in the time
Terminate at t3'.X-ray tube 30 can be completely discharged at time t4.
Using timing shown in Fig. 6, it is spaced shown in t' from such as Fig. 3 in the additional exposure during time interval t''
Additional exposure in significantly reduce.It should be noted that the complete electric discharge of x-ray tube 30 may not be needs in each application
's.For example, before next driving of power switch 15, it may be sufficient to allow the partial discharge of x-ray tube 30.This is only in exposure
In the case of the small compromise of duration, the faster switch response for x-ray tube 30 can be allowed.
The present invention has been described in detail, and may have been described with particular reference to suitable or presently preferred embodiment
The present invention, but it is to be understood that can realize change and modification within the spirit and scope of the present invention.Presently disclosed implementation
Therefore example is considered illustrative and not restrictive in all respects.The scope of the present invention indicates by appended claims,
And all changes fallen into the meaning and range of its equivalent are intended to be included therein.
Claims (16)
1. a kind of x-ray imaging device comprising:
Voltage generator may be switched to connect when the generator is switched on and penetrate across the x-ray anode and x of x-ray source
The activation voltage of line cathode, and may be switched to disconnect when the generator is disconnected across the anode and the cathode
The activation voltage, the x-ray source is configured as emitting ionizing radiation when the activation voltage is switched on, and configures
For the transmitting for cutting off the ionizing radiation when the activation voltage is disconnected;And
Discharge cell, is electrically connected to the x-ray source, and the discharge cell includes for being disconnected in the activation voltage
When the anode is electrically connected to the cathode to the discharge circuit that discharges of activation voltage;
Wherein, the discharge cell include with electric discharge tube anode and discharge tube cathode vacuum discharge tube, the discharge tube with
The mode in parallel with the x-ray tube is electrically connected to the voltage generator, and wherein, discharge tube conduction electric current with
It discharges the activation voltage.
2. imaging device according to claim 1, wherein the discharge cell includes being broken in response to the activation voltage
It opens with the charge/discharge control circuit to the filament of the discharge tube to electricity, the filament is arranged to and the electric discharge tube cathode phase
Neighbour, and wherein, the discharge tube conducts the electric current when to the filament to electricity.
3. imaging device according to claim 2, wherein electric discharge tube anode rotation when being powered.
4. imaging device according to claim 1, wherein the discharge cell is spaced apart with the voltage generator.
5. imaging device according to claim 1, wherein the discharge tube includes oil coolant.
6. imaging device according to claim 1, wherein the x-ray source occurs via cable connection to the voltage
Device, and wherein, the electric current for discharging the activation voltage includes the electricity generated by the capacitor of the cable
Stream.
7. a kind of method for x-ray imaging, this method include:
Voltage generator is activated, including provides voltage from the voltage generator across x-ray tube and is receiving the electricity
Ionizing radiation is emitted by the x-ray tube when pressure;
Discharge circuit is electrically connected to the voltage generator in a manner of in parallel with the x-ray tube;And
The voltage generator is disconnected and to the discharge circuit to electricity, including across described in the discharge circuit short circuit being powered
X-ray anode and the x-ray cathode;
Wherein, to the discharge circuit in the step of electricity, the filament of the vacuum tube into the discharge circuit includes making to electricity
Electric current conducts the gap between the anode and cathode of the vacuum tube.
8. according to the method described in claim 7, wherein, the anode of the vacuum tube includes the target of non-tungsten material.
9. according to the method described in claim 7, this method further includes repeating the steps of:Activate the voltage generator;It is disconnected
Open the voltage generator;And to the filament of the vacuum tube to electricity it is one or many so as to by fluoroscopic image or based on
The object for calculating tomography is imaged.
10. a kind of method for x-ray imaging, this method include:
Voltage generator is activated, including provides voltage from the voltage generator across x-ray tube and is receiving the electricity
Ionizing radiation is emitted by the x-ray tube when pressure;
Discharge circuit is electrically connected to the voltage generator in a manner of in parallel with the x-ray tube;And
The voltage generator is disconnected and to the discharge circuit to electricity, including across described in the discharge circuit short circuit being powered
X-ray anode and the x-ray cathode;
Wherein, to the discharge circuit in the step of electricity, electrically multiple dielectric fillers into the discharge circuit
To electricity, the container of the dielectric filler is electrically connected container in series, including to be conducted through electric current the multiple
The container of dielectric filler.
11. according to the method described in claim 10, wherein, the container of the dielectric filler is usually spherical.
12. according to the method described in claim 10, this method further includes repeating the steps of:Activate the voltage generator;
Disconnect the voltage generator;And electrically to the container of the multiple dielectric filler to electricity it is one or many so as to
It is imaged in the object of fluoroscopic image or computed tomography.
13. a kind of x-ray imaging device comprising:
Voltage generator including switch, the switch are configured as switching on and off the voltage generator;
X-ray tube including anode and cathode, the x-ray tube are electrically connected to the voltage generator, the x-ray tube quilt
It is configured to emit ionizing radiation when the voltage generator is switched on after voltage generator described in Shi Cong receives voltage, and
And it is configured to cut off the transmitting of the ionizing radiation when the voltage generator is disconnected;And
Discharge cell is electrically connected to the x-ray tube and is electrically connected to the switch, and the discharge cell includes using
In the discharge circuit that the anode is electrically connected to the cathode when the voltage generator is disconnected;
Wherein, the discharge cell is electrically connected to the voltage generator in a manner of in parallel with the x-ray tube, described to put
Electric unit includes the container for the multiple series connections for remaining at dielectric fluid.
14. imaging device according to claim 13, wherein each of described container is spherical.
15. imaging device according to claim 13, wherein the discharge cell includes being electrically connected in the container
Each discharge controller so that voltage pulse to be delivered to each of described container in parallel.
16. imaging device according to claim 13, wherein the x-ray tube is sent out via cable connection to the voltage
Raw device, the cable store charge caused by the natural capacity due to the cable, and wherein, when the discharge circuit will
Stored charge is discharged when the anode is electrically connected to the cathode.
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