CN201551320U - Power supply used for portable radiographic detector - Google Patents
Power supply used for portable radiographic detector Download PDFInfo
- Publication number
- CN201551320U CN201551320U CN2009201791940U CN200920179194U CN201551320U CN 201551320 U CN201551320 U CN 201551320U CN 2009201791940 U CN2009201791940 U CN 2009201791940U CN 200920179194 U CN200920179194 U CN 200920179194U CN 201551320 U CN201551320 U CN 201551320U
- Authority
- CN
- China
- Prior art keywords
- power supply
- detector
- digital radiography
- store electricity
- inducer
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Images
Landscapes
- Apparatus For Radiation Diagnosis (AREA)
- Measurement Of Radiation (AREA)
Abstract
The utility model provides a power supply used for a portable radiographic detector. The digital radiographic detector comprises a two-dimensional photoelectric sensor array that is arranged by lines and rows. A plurality of signal conductor wires are connected with the photoelectric sensor and extend along the two-dimensional array in the first direction. A switch power is connected with the power supply and is provided with a first memory inductance and a second memory inductance, wherein the first memory inductance and the second memory inductance are basically matched with each other and are electrically connected with each other in series; and the power supply is also provided with a magnetic flux field with reversed phases, wherein the magnetic flux fields are aligned to the first direction of the signal conductor wires.
Description
Technical field
This utility model relates generally to the digital radiography imaging system, and relates to the digital radiography receptor with on-board switching power supply in particular.
Background technology
Usually, for polytype electronic detecting device, especially for portable digital radiography imaging detector, the wireless performance of portable, battery powered is just becoming the performance of expectation.For medical imaging receiver apparatus, portable radio operation provides the hope that improves patient care, has the advantage that comprises improved workflow and apparatus adaptability.
Digital radiography (DR) detector also is known as flat-panel detector (FPD), by the ability of quick visualization and transmission radioscopic image is provided, has started the revolution in general radiography field.Patient's X-ray sheet can be sent to one or more long-range mechanisms by data network effectively, so that the radiologist analyzes and diagnosis, has avoided sending by mail or Messenger and has passed the delay that physical film is brought to radiologist at a distance.
Fig. 1 has shown the part sectioned view of the basic image device of conventional FPD.FPD generally comprises a large-area two-dimensional image sensor array 10, and this two-dimensional image sensor device array 10 has thousands of the radiation-sensitive pixels 14 that are configured to the ranks matrix.Each pixel 14 has one or more photoelectric sensor 12 and one or more switch elements 16 such as thin film transistor (TFT) (TFT) such as PIN photodiode.Be generally understood as, photoelectric sensor converts the X ray radiation by the signal in the memorizer that switch element 16 is read and is stored in detector is associated to.This traditional DR disposes by using the conducting metal row and column across dull and stereotyped length of detector and wide extension, and permission is addressed individually to each radiation-sensitive pixel 14 and is read out.
The radiation-sensitive pixel 14 of FPD uses the photodiode such as PIN photodiode usually, but also can use other photoelectric sensor technology.When photodiode was used for the radiography detection, the X ray radiation at first was converted into the wavelength that is suitable at the photodiode of each radiation point.By using scintillation screen 15 to finish, scintillation screen 15 is according to the photon in second wavelength of stimulated emission in the photodiode sensitivity of the X ray radiation of a wavelength usually for this.Then, the electric charge that is directly proportional of the photon numbers that each photodiode produces with it receives.Detect the X ray radiation by this way, detected ray is converted to digital information, and the process of storage inside digital information is called as image acquisition here.In case collect radioscopic image, this image is sent to operator's console from FPD, so that image evaluation, downstream distribution and/or longer-term storage.
Traditionally, large-scale digital radiography device, FPD forever is installed in the precalculated position and is used for imaging patients.The installation of this class type generally is set at the regular set that obtains the radioactivity image that a large amount of patients conventionally need.Yet under the situation of the non-standard image of needs, patient locatees with respect to fixed DR detector.Concerning some patients, this has just produced the problem that digital radiography is not easy to solve, even must use old technology, for example fluorophor computed radiography (CR) X ray box.This can cause the cost and the poor efficiency that increase, also requires medical institutions' maintain old equipment so that handle the imaging type that is difficult to carry out in the DR system.
Portable box type FPD provides the replacement scheme of orientation problem, allows littler more portable x-ray imaging system.Because detector can be placed into patient after one's death easily, and do not require posture that patient takes inconvenience so that imaging, portable FPD has improved the work efficient of flow process of operator.Under a lot of situations, because the similar detection device can be used for wall mounted position and horizontal table position, FPD can replace the demand of multiple detector.Portable FPD has motility, moves to the position of any appropriate of DR suit quickly and easily, and the radioscopic image that immediate access obtained also is provided.
The progress of electronic component and encapsulation technology makes portable box type detector become possibility, allows the obvious minimizing of overall dimensions and weight.For example in U.S. Patent No. 5,844, box type FPD has been described in 961, it has generally described the no film digital X-ray box that its external dimensions is approximately equal to the size of the X-ray film of normal size or CR box.Combined communication and electric power connection line or electric wire are as from FPD transmission of digital view data with to the device of board device supply power supply.External AC to DC power supply also is connected to box by combined communication and electric power connection line.Power supply such as battery selectively is positioned at box inside so that overcome the inconvenience of the direct line connection that need be used for this purpose.
United States Patent (USP) 7,015,478 is entitled as " X-ray Imaging Apparatus " (Yamamoto), and the portable electronic box type detector of the interconnected electric wire with the communication of providing and power supply has been provided.This patent has been described second wire has been connected to box, connects when being placed on below the patient with convenient detector and separates this equipment.Battery and power supply can be positioned at the detector frame.
The wired solution of introducing in the patent such as people such as McEvoy and Yamamoto has inborn shortcoming.Need all connect and keep connection at each end of interconnected electric wire, as mobile FPD around the patient and during the back at some position, this is difficult to accomplish.When trying optimization ground below patient during positioning box type FPD, electric wire can become obvious obstacle.At the mobile FPD electric wire of may catching because of carelessness or stumble during to reposition, so electric wire also is the latency that causes checkout equipment to damage.Electric wire has also limited the distance that detector can leave control station.Other problems relates to a plurality of DC level demands that are used to detect with the different piece of treatment circuit.Because these reasons, wired DR imaging flat board has special difficulty.
In order to remove cable power effectively, need compact, light, can continuous operation power supply on the portable plates of a few hours.For example, generally have the high energy lithium polymer battery of two or more batteries that are connected in series, can provide the enough energy for the composite communication on the portable FPD, control and imaging circuit.Switched-mode power supply (SMPS) be a kind of DC to the DC transducer, its uses battery and can produce the output voltage that is below or above the voltage that battery provides.Generally there is polytype DC to be used for SMPS equipment, and known by the technical staff of electronic applications to the topological structure of DC transducer.The example of some these topological structure is blood pressure lowerings, boost, SEPIC, CUK, reverse and forward converter.
SMPS comes work by periodically switching to enter into as the induction apparatus of energy storage elements and the electric current of capacitor.Because the storage of their energy can be relative less with switch element, SMPS equipment is Comparatively speaking compact and in light weight.Simultaneously, the energy conversion efficiency high energy of SMPS equipment reaches 95%.
Although SMPS has these advantages, it also has significant disadvantage.Than linear power supply actuator and other power supply types, the high noise level of self is one of these shortcomings.The noise that is produced by the SMPS switch can be conducted and be radiated, and produces significantly to disturb and pseudo-shadow, reduces the performance of peripheral device, subsystem or circuit, particularly aspect signal to noise ratio (snr).This influence is to such as having the DR detector, and the high impedance detector circuit package is very particularly evident near the sensitivity equipment of the inducer on the SMPS.
Main type from the electromagnetic induction (EMI) of Switching Power Supply is to be created in the radiation electromagnetic field that is close to switching device.Used many traditional methods to minimize the EMI effect of SMPS.To conduction formula EMI pattern, need to use extra filter device, increase along conductive path series connection near power supply input and output line.These filter devices generally comprise capacitor and placed in-line ferrite inductor, are used for shunting before high-frequency energy conducts to peripheral circuit or absorbing this high-frequency energy.
It is to make the switching frequency of one or more switched-mode power supplies and other timing waveforms that have been used for electronic equipment or main internal clocking synchronous that general another kind with the use of noise filter combination of devices reduces to conduct electricity formula EMI method.For example, timing waveform can be to be used for the triggering sensitive operation that sampling keeps measurement, charge transfer and small-signal modulus (A/D) conversion.All switched-mode power supply and common clock synchronously or move owing to interference noise is limited to a public frequency section, can be simplified the realization of wave filter on common clock in device.Use is synchronized with the switched-mode power supply of main system clock, can regulate sequential from the transient noise of switching mode PWM waveform to prevent producing transition in the process of sensor operation.As the example of a sequential simultaneous techniques, U.S. Patent No. 4,034,232 have described the method that phase shift clock separately on synchronous a plurality of power supply and the position minimizes destructive transition.
Because the radiation noise may come near a plurality of different source EMI sensitive circuit or the subsystem, the inhibition technology that radioactivity EMI propagates is a comparison difficulty and expensive.The scheme of traditional minimizing radiation EMI comprises by shielding protection sensitive circuit device.Because radiation EMI has electrical device and magnetic device, need to use two types shielding.Ground level and faraday cage have been used to the E field shield, and shunting also reduces the E field significantly effectively.To magnetic H field device, used thick ferromagnetic material to come the shunt stray magnetic flux and make it avoid being coupled into the responsive lead of peripheral circuit with high osmosis such as Mu metal, iron-nickel alloy.
Although being packaged into, SMPS meets the narrow restriction of portable DR detector, integrated these noise power supplys in the detector frame and do not introduce especially challenge of interference.Avoid the demand of electric conductivity that SMPS produces and radioactivity EMI significantly to increase the size and the weight requirement of wireless DR detector.The filter device that is used for the conducted noise compensation that increases has increased overall cost, the size and sophistication of SMPS.Traditional H field shield scheme that is used to solve the radiation noise comprises the Mu metal, and is invalid at employed high switching frequency place.Promptly allow to find suitable shielding material, shielding can increase equipment size and weight significantly.
Therefore, need the digital image detector of improvement, this digital image detector comprises SMPS power supply on the plate, but can not be subjected to the EMI influence and the generation image deterioration.
The utility model content
The purpose of this utility model is, solves the needs of the switched-mode power supply with the EMI that reduces.According to this purpose, an aspect of the present utility model provides the digital radiography detector that comprises with 2 D photoelectric inductor array, a plurality of holding wire and the Switching Power Supply of row and column configuration.A plurality of holding wires are connected to photoelectric sensor and extend along the first direction of two-dimensional array.Switching Power Supply is connected to power supply and comprises that first and second store inducers, and this first and second stores inducer and mate basically and be connected in series, and comprises the flux field that phase place is opposite, and basically along the first direction alignment of holding wire.
An aspect of the present utility model provides a kind of digital radiography detector, comprising: press the 2 D photoelectric inductor array that row and column is placed; Many signal conductor connect described photoelectric sensor and extend at first direction along described two-dimensional array; And Switching Power Supply, be connected to power supply and comprise the first and second store electricity sensors, the wherein said first and second store electricity sensors mate substantially, electrically series connection, comprise the flux field that phase place is opposite, and basically along the described first direction alignment of described signal conductor.
Of the present utility model being characterised in that, above-mentioned digital radiography detector further comprises the second switch power supply that is connected to described power supply, and comprise the third and fourth store electricity sensor, the wherein said third and fourth store electricity sensor mates basically, electrically series connection, comprise the flux field that phase place is opposite, and basically along the described first direction alignment of described signal conductor
Of the present utility model being characterised in that, the first and second store electricity sensors and this third and fourth store electricity sensor are staggered in the above-mentioned digital radiography detector.
Of the present utility model being characterised in that, the first and second store electricity sensors separate fully with this third and fourth store electricity sensor in the above-mentioned digital radiography detector, make this magnetic field of this first and second store electricity sensor and this magnetic field non-interference of this third and fourth store electricity sensor.
Of the present utility model being characterised in that, the first and second store electricity sensors are positioned in the first of these many signal conductor in the above-mentioned digital radiography detector, and this third and fourth store electricity sensor is positioned on the second portion of these many signal conductor.
Of the present utility model being characterised in that, power supply described in the above-mentioned digital radiography detector is the rechargeable battery that is placed on the described digital radiography detector.
Of the present utility model being characterised in that, power supply is wiredly connected to described detector by cable described in the above-mentioned digital radiography detector.
Of the present utility model being characterised in that, this cable transmission of data signals between digital radiography detector and external source further in the above-mentioned digital radiography detector.
Of the present utility model being characterised in that, above-mentioned digital radiography detector further comprises wireless data interface.
Of the present utility model being characterised in that, above-mentioned digital radiography detector further comprises processor, and described processor is configured to drive the adjustable timing off-set between the signal and the sequential of sampled signal for described photoelectric sensor array provides Switching Power Supply.
Of the present utility model being characterised in that, Switching Power Supply described in the above-mentioned digital radiography detector be blood pressure lowering, boost, oppositely, in chopper circuit or the push-pull type power supply one.
Of the present utility model being characterised in that, Switching Power Supply is synchronized with the master clock of reading circuit described in the above-mentioned digital radiography detector.
An aspect of the present utility model provides a kind of method that power supply is provided to digital radiography detector, wherein said digital radiography detector comprise the 2 D photoelectric inductor array of placing by row and column and be connected to described photoelectric sensor and along described two-dimensional array in the upwardly extending many signal conductor of first party, described method comprises: DC is provided power supply; Switching Power Supply is connected to described power supply, described Switching Power Supply comprises the first and second store electricity sensors, the wherein said first and second store electricity sensors mate substantially, electrically series connection, and comprise the flux field that phase place is opposite, and along the direction substantial alignment that parallels with described many signal conductor of described digital radiography detector; And skew is used to respond to the signal saltus step of sampling control signal of equipment of described detector and the switch saltus step of described Switching Power Supply.
Of the present utility model being characterised in that, DC power supply described in the above-mentioned method is the battery that is placed on the described radiographic detector.
Of the present utility model being characterised in that, above-mentioned method further comprise adjusts this skew.
Of the present utility model being characterised in that provides and uses paired inductance to offset the Switching Power Supply of mutual leakage magnetic flux field.
Advantage of the present utility model is, a kind of design of Switching Power Supply is provided, and allowing compact package and can being used to has the electronic installation that reduces the emf shielding requirements.
By reference following DETAILED DESCRIPTION OF THE PREFERRED and appended claim, more clearly understanding and cognition these and other aspects of the present utility model, purpose, feature and advantage.
Description of drawings
Description to be specifically to indicate and clearly to protect the claim ending of this utility model theme, believes in conjunction with the accompanying drawings and following description, will understand this utility model better.
Fig. 1 is the part sectioned view of the imaging sensing element of traditional DR imaging flat board.
Fig. 2 is the partial schematic block diagram that is used for the radiographic X image inductor array of DR traditionally.
Fig. 3 illustrates the schematic block diagram that obtains the signal path of signal from each pixel.
Fig. 4 is the schematic block diagram of traditional switched-mode power supply.
Fig. 5 A is the perspective view of the shared ferrite inductor device of traditional switched-mode power supply.
Fig. 5 B is the part sectioned view of inducer among Fig. 5 A.
Fig. 6 A has shown the inducer magnetic field on every side of Fig. 5 A
Fig. 6 B has shown the magnetic field along the outside radiation of circuit lead of Fig. 6 A.
Fig. 7 shows the schematic block diagram according to the Switching Power Supply of the use of preferred embodiment of the present utility model coupling and reverse inducer.
Fig. 8 is the perspective view of two inducer alignment and respective poles.
Fig. 9 shows the timing waveform of reciprocal EMF signal from cancellation effect.
Figure 10 is the two inducers relevant with the circuit lead plane graphs that align.
Figure 11 shows the plane graph of in pairs two inducer alignment, a pair of each Switching Power Supply that is used for.
Figure 12 is the DR detector perspective section view according to this utility model embodiment.
Figure 13 shows the sequential chart that concerns between the control signal of the picture signal collection that is used for every capable pixel.
Figure 14 shows the sequential chart to the possible sensitivity of switching transient of no slight phase shift.And
Figure 15 shows the sequential chart of minimizing to the Switching Power Supply phase shift of the sensitivity of switching transient.
The specific embodiment
The element that is interpreted as not illustrating especially or illustrate can adopt and well known to a person skilled in the art various forms.
Apparatus and method of the present utility model provide a kind of digital radiography (DR) detector with switched-mode power supply (SMPS), and it helps to reduce the EMI of peripheral circuit.Certain methods to provide the EMI effect to offset certainly in the DR detector frame is provided SMPS of the present utility model, otherwise the EMI effect can be introduced in the coupled signal lead of digital detector.
DR detector circuit structure
In order to understand the problem difficulty of power supply on the plate that is used for DR detector flat board, at first the detail knowledge detector circuit is that what how to dispose is useful.Fig. 2 has shown the sketch map of the fraction of image sensor array 10 in traditional DR detector, and wherein image sensor array 10 forms the matrix of the pixel of describing 14 in Fig. 1.Pixel 14 indications are in frame of broken lines.Each pixel 14 comprises the photoelectric sensor 12 such as photodiode, and is paired with the switch element 16 such as TFT.Each photoelectric sensor 12 can optionally be connected to row sense wire 22 by its associated switch element 16.Among Fig. 2, pixel 14 have photodiode as photoelectric sensor 12 and TFT as switch element 16; Photodiode cathode switches to row sense wire 22 by TFT.The TFT grid is controlled on the line 20 by corresponding gate drivers in the gate drivers array 18.Photodiode anode is connected to common bias source 34 by lead 24.When some line 20 drives particular rows, all photodiodes in this row are connected to corresponding conductive column sense wire by TFT or other switch elements 16 that is associated.Then, the electric charge of each photodiode is sent in one group of charge amplifier 26 one.The electric charge of each photodiode is proportional with the amount of light that strikes particular photodiode from (Fig. 1) of DR receptor scintillation screen 15.Amount of light is directly proportional with the X ray quantity that receives on the imaging detector specific region successively.Therefore, all photodiodes in sensor array are all processed, formed the bidimensional analog image of expression patient radioscopic image.
26 pairs of electric charges from corresponding photodiode or other photoelectric sensors 12 of each charge amplifier carry out integration, and the voltage that is directly proportional with electric charge is provided.This voltage transmits by the input that signal bus 30 is used as the multiplexer (MUX) 32 of A/D converter 28.A/D converter 28 becomes respective digital numerical value with the voltage transitions of output place of each charge amplifier 26, is stored to the memorizer (not shown) then.In case use this method to read all pixels 14, for example, the radioscopic image data of generation can temporarily deposit the local memory unit of DR detector in.At this point, the two-dimensional image data of generation is sent to ppu from detector or operating console carries out entry evaluation.From there, view data can be as required further by downlink transfer in case diagnosis and long term archival store.
The schematic block diagram of Fig. 3 has shown the signal path that is applied to from the picture signal collection of each pixel, still uses the example of photodiode as the photoelectric sensor 12 that receives light λ.The negative electrode of photodiode is connected to the TFT transistor drain that is associated with it as switch element 16.The TFT source terminal is connected to the input of corresponding charge amplifier 26 by row sense wire 22.Every row sense wire 22 all has a corresponding distribution capacity and resistance 54.The TFT grid is connected to the gate drivers 50 of gate drivers array 18 (Fig. 2) by gate drivers line 52.Gate drivers line 52 also has along the electric capacity of its distribution of lengths and resistance.Yet because its Low ESR and numerical characteristic, this line is generally unlike so responsive to electromagnetic interference as analog signal line.Charge amplifier 26 comprises the associated switch 56 of cross-over connection integrating condenser 58.When switch 56 (cuts out) under low resistive state, it carries out short circuit to capacitor 58 effectively, and makes the output zero setting of charge amplifier 26 or restart the output of charge amplifier 26.Because the inherent offset voltage of charge amplifier circuit, the voltage when restarting will can strictness be not zero.When switch 56 (is opened) under high-impedance state, 26 pairs of charge amplifiers are from the charge integration of photodiode and convert voltage to, and this voltage is applied to correlated-double-sampling (CDS) circuit 60.The voltage of charge amplifier 26 is directly proportional with the amount of light that strikes photodiode, and this amount of light adds charge amplifier 26 inherent offset error voltages again with proportional at this locational X ray radiodensity.
The output of 60 pairs of voltage amplifiers 26 of CDS circuit is sampled, and under two kinds of different conditions this sampling is sent to MUX 32.CDS circuit 60 has two sampling capacitors 62,64, and each has corresponding switch 66,68.When switch 56 cut out, short circuit integrating condenser 58 carried out first sampling of induced signal offset error when charge amplifier 26 is restarted.The second time sampling that comprises the same skew that adds picture element signal is opened with charge amplifier 26 at switch 56 and is carried out after photoelectric sensor 12 accelerated chargings by energy-storage capacitor 58.Close switch 68 and allow Charge Storage, the voltage signal across capacitor 64 is provided.Two voltage signals from CDS circuit 60 are selected by MUX 32, subtract each other, and are sent to A/D converter 28, and voltage difference is converted into digital value in A/D converter 28.Subtracting each other before integration removed the offset voltage that exists in the charge amplifier 26.The result can be stored in the digital memory (not shown) of imaging detector electronic device then.
Integrated circuit structure that shows among Fig. 2 and Fig. 3 and image acquisition signal path have shown why the DR detector very easily is subjected to influence of noise.Some obvious noise are considered as follows:
(i) be microampere order by the electric current that produce and that switch to sense wire 22 of the photodiode on the column wire 24, therefore slight noise also is unsuitable.
(ii) sense wire 22 has the high resistant characteristic.Be extended to the total length (wide) of image-position sensor array 10 and be connected to charge amplifier 26, according to each length in thousands of row sense wires 22 of existing DR slab design up to 43 centimetres or longer.The external noise that the combination of high impedance and length makes row sense wire 22 be subjected to time-varying magnetic field especially easily disturbs, and wherein close pixel 14 of this time-varying magnetic field or close conduction sense wire 22 radiate.
(iii) bias generator 34 leads such as conductive wire 24 have high-impedance behavior, are subject to spuious time-varying magnetic field influence.
(iv) capable lead, line 20 also is subjected to the influence of these same time-varying magnetic fields.Yet the row lead is connected to the gate drivers of gate drivers array 18, than the impedance circuit of row conductor, and the impedance circuit that it is normally lower.In addition, the row signal is the threshold number signal, therefore than the signal of row conduction sense wire 22 to being to the low responsive order of magnitude of external noise.
(lead of signal bus 30 that v) output of charge amplifier 26 is sent to MUX32 and A/D converter is responsive more to noise, because these lines are analog signal lines.These all are subjected to the interference of radia magnetic field easily, but because the low output impedance of charge amplifier 26 itself is often more insensitive than row sense wire 22.
(vi) in two kinds of above-mentioned sampling work processes, make the correlated-double-sampling operation to noise-sensitive to signal being switched to sampling capacitor 62,64 needed sequential and signal sampling work.That is to say,, in the switching transient process, still have the risk of some noise jamming even correlated-double-sampling itself can reduce the influence of induced noise signal.
Generally speaking, the normal structure of large tracts of land high impedance visual detector makes it be subject to the EMI influence.What be worth expectation is, reduce from other circuit in the radiographic detector, especially the closing signal line and with these signals transmission so that storage and the circuit measured, the external noise of work.Take to shield with additive method and reduce EMI as much as possible, so that the signal to noise ratio that reduces noise level and provide diagnosing image to need near source.
Because the power supply of mentioning itself has high EMI level before, the on-board switching power supply that uses in the DR detector is just in time opposite with these requirements.When the requirement of the light weight of considering the DR receptor and cramped construction, these problems become more sharp-pointed.
In order to understand equipment of the present utility model is how to solve these noise problems, and overall structure and the work of describing the DC-DC Switching Power Supply are helpful.The rough schematic view of SMPS100 has shown the integrated circuit topological structure that is used in usually in these power supplys among Fig. 4, has shown element and some exemplary signal waveforms of using in this class circuit.Battery 84 provides power supply through filter capacitor 86.ON-OFF control circuit 80 is optionally switched two solid-state switches, is shown MOSFET power transistor 82a, 82b in Fig. 4, the voltage waveform 94 by diode 88 is provided and controls the electric current 98 of inducer 70.Electric current by inducer 70 is to be similar to triangle oblique wave 96 shown in Figure 4.The switching frequency place that the switch current that occurs in the inducer 70 is created in power supply is (t) magnetic flux of changing on amplitude in time.This frequency numerical range is from more than hundreds of hertz to 1 megahertz in the design of various switching modes.ON shown in waveform 94 is to the dutycycle decision of OFF time or the output voltage of adjusting filter capacitor 90 and load 92.Thereby switching mode control circuit 80 comes the voltage of existence in the regulating load 92 by the output voltage of being monitored inducer 70 by the feedback line (not shown).
Usually, the energy storage elements as the energy storage element that uses among the SMPS100 is a ferrite inductor.How Fig. 5 A has shown usually package inductance device 70.If be used for switched-mode power supply, inducer 70 is so constructed the magnetic flux that bleeds the inductor coil peripheral region with minimizing usually.The part sectioned view of Fig. 5 B has shown the configuration of inductor coil 72 around the center of Ferrite Material.
Consider design and encapsulation technology, inducer 70 can radiate and cause the interferential magnetic field of peripheral circuits signal.Fig. 6 A has shown that distribution is owing to flux leakage and in inducer 70 general toroidal magnetic field 74 on every side.The description type in magnetic field 74 is rough approximations among Fig. 6 A, rather than accurately describes the illustrative purposes that is used for discussing below.
The direction in magnetic field 74 or the arctic (being expressed as N), or the South Pole (S) are formed at the end of inducer.The magnetic field 74 that Fig. 6 B has described same inducer 70 and outwards radiated along lead 78, wherein lead 78 extends along near the path the lead.Lead 78 is operated near the switched-mode power supply inducer 70, passes or connect the line in the magnetic field 74 of inducer 70.So, lead 78 is because the magnetic flux of the variation in magnetic field 74 is subjected to the influence of induced voltage easily, and is quantitative according to Faradic electricity magnetic induction, is expressed as follows usually:
Herein, ε is induction electromotive force (emf), and unit volt, φ are magnetic flux, the unit weber.Lead 78 should be a sense wire 22.In this case, flux leakage may be increased to signal content with noise.
The induced voltage of noticing the inducer with time-varying magnetic field from this equation is directly proportional with the time rate of change of the magnetic flux that is connected inducer.The ampere-turn multiplication by constants of coil 72 is long-pending proportional in magnetic flux and the inducer 70.The occurrence of constant is by the concrete structure of ferrite inductor 70 and the various parameter decisions relevant with the air gap size with the Ferrite Material particular type.
Be back to Fig. 6 B, the rate of change dI/dt of current waveform in the coil 72 is because the flux leakage around the inducer 70 has produced d φ/dt or time-varying magnetic field 74.This time-varying magnetic field goes out corresponding emf voltage at lead 78 internal inductions that connect this magnetic field.
Shown in electric current Figure 96 of Fig. 4, concerning DC to the DC converter topologies of some types, the induction field amplitude also comprises the AC component except comprising the DC component that is called as the DC bias voltage.The AC component is known as on " riding over " DC bias level.The AC weight sense in magnetic field should cause the noise voltage of sensitive conductive circuit around just.
Therefore, Fig. 2 to 6B discusses as the aforementioned, uses switched-mode power supply that significant disadvantages is arranged at the signal conductor adnexa.For example, the magnetic flux change that is produced by the electric current that flows through inductor coil has produced corresponding emf voltage, and this emf voltage is introduced into and is in inducer lead on every side.Further along signal processing path descending (with reference to shown in Figure 3), this induction emf voltage and any detector signal voltage addition that in row are read lead, exists.This extra emf voltage is the noise source that a kind of artificial disturbance the most at last is introduced into the detector output image.
The traditional shielding or the method for inhibition are difficult to use or be not enough to satisfy the demands, especially the demand of compactness and light weight design.The distance that increases between inducer and the lead is a kind of scheme opposite with Compact Design.Similarly, be unpractical for signal conductor provides sufficient shielding.Although used some shieldings, extra shielding can increase size and weight; And high switching frequency does not allow to use multiple traditional shielding material.
Embodiment of the present utility model is by introducing the problem that anti-emf solves induced emf, and this has offset the flux field that produces on the holding wire at least partially in the switched-mode power supply circuit.The schematic block diagram of DR detector 190 has been described this how first embodiment by using placed in-line inducer that 70a, 70b are realized in SMPS200 among Fig. 7.In this scheme, inducer 70a, 70b are basic couplings, that is to say, essentially identical inductance are arranged, but are configured to same switching current is provided the relation of reverse phase.The switch mode operation of SMPS 200 meets the same common-mode of describing with reference to the SMPS100 among the figure 4, and for example, battery 84 uses together on energy and the plate, also optionally uses by wired power supply with outside DC source 44.By the accumulate sensing element, be made up of placed in-line two inducer 70a, 70b here by this accumulate sensing element with conduction of current for the switch element of ON-OFF control circuit 80 driving power transistor 82a, 82b or other types.(the load that load 92 expressions are seen from the SMPS200 functional perspective, because provided the actual components of power supply can comprise at least a portion or illustrated a part of logical device the array 10 from circuit) shown in Fig. 7 and sequential chart subsequently, control logic processor 120 is coordinated from the sequential of the switching signal of ON-OFF control circuit 80 with by the sampled signal from imaging sensor array 10 of master clock 230 controls.
But, exist obviously different between the conventional switch mode power embodiment that in the embodiment of Fig. 7 and Fig. 4, gives an example.To be apparent in view difference below:
(a) inducer 70a, 70b are placed in-line, but it is reverse with the electric current 98b by inducer 70b to connect into the electric current 98a that is used for current switching that makes by inducer 70a.Inducer 70a, 70b approximate match make that each inducer is half of the required overall inductance of Switching Power Supply.
(b) owing to the electric current by inducer 70a, 70b is reverse, inducer 70a produces leakage magnetic flux field 104a, and it becomes 180 degree anti-phase with leakage magnetic flux field 104b that inducer 70b produces.Flux field 104a, 104b amplitude are identical, and phase place is opposite.This is also shown in the waveform 96a (corresponding to inducer 70a) and waveform 96b (corresponding to inducer 70b) separately.Net effect is meant that the induction emf of a tittle is cancelled, and especially along near the path of lead 78, one of them is represented as by flux field 104a, 104b.
(c) inducer 70a, 70b along the path of lead 78 by alinement.That is to say that in order to offset the influence of induction emf most effectively, two inducer 70a, 70b Ying Zaiyu are leads 78 along nearest induction coupling signal wire here, the identical direction of direction on align.With reference to the perspective view of figure 8, lead 78 is that the D direction is extended in the direction of inducer 70a, 70b alignment, so that offset for peripheral lead 78 provides the most effective emf.Herein, inducer 70a, 70b are coupled on an equal basis with lead 78 basically.
What (d) inducer 70a, the 70b of coupling should be enough mutually makes that closely their part magnetic field is overlapping.Excessive distance can reduce the benefit from cancellation effect between inducer 70a, the 70b.
Timing waveform shows isolating phase place (φ among Fig. 9
1, φ
2) and emf (emf
1, emf
2) signal, they are combined so that be provided for the synthetic emf signal (emf of emf compensation
Res). Waveform 106a, 106b have shown the flux field of the variation of inducer 70a, 70b separately.Emf waveform 108a, 108b shown produce by this flux change and respectively with the electrically conductive signal lead 78 coupled induction emf signals of inducer 70a, 70b.Any induced induction emf voltage in lead 78 all is the noise error source, this error causes the pseudo-shadow at radiographic detector easily, but when two induction emf voltages exist simultaneously in same adjacent domain, and along same holding wire alignment, then clean and the counteracting that needs is provided, have to residual error emf
ResWaveshape signal 108c, this residual error emf
ResWaveshape signal 108c is little more a lot of than independent emf waveform 108a or emf waveform 108b.
The plane graph of Figure 10 is the vertical view that shows that inducer 70a, 70b accurately align on lead 78.Show three leads 78.Can see in the image detection apparatus of reality, below each inducer or extensible hundreds of bar lead arranged on every side.Therefore, each the right inducer that preferably makes inducer equally is positioned near same group of lead, that is to say, along the main direction alignment of the holding wire of digital image detector.
Shown in Fig. 7-10, single inductor is used for each switched-mode power supply to 70a, 70b.Power supply in order to provide various logic, processing and sensor circuit to need is provided, may needs many different voltages such as the complex appts of radiographic detector.Therefore, can comprise a plurality of switched-mode power supplies in the single DR detector, each power supply has the inducer of oneself right.In this case, preferably keep apart inducer and separate the field cancellation effect that near the inducer can not disturbing like this is right so that suitable distance is interlaced with each other making them.The vertical view of Figure 11 has shown that possible inducer is to placing example.Shown that herein two inducers are to 110a, 110b.In order to obtain suitable performance, place first and second inducers and they can be on the same lead 78 110a, 110b.If possible, purpose is two or more inducers of preventing to be coupled to same lead group to having two residual error voltages, because this error voltage that can make on the lead to be produced doubles, and increases because the graphics artifact shadow that bigger residual error voltage causes.
Figure 12 has shown the embodiment of portable DR detector 190.Herein, a series of electrically conductive signal leads 78 length of on direction V (locating vertical direction), having extended DR detector 190 with the tradition of DR detector 190.Orthogonal with vertical direction V is horizontal direction H.The whole sensitive surface of DR detector 190 has the array of bidimensional pixel 14; The perspective view of Figure 12 shows small number of pixels point 14, but not to scale.Also provide wave point 40, so that DR detector 190 is complete portable imaging flat boards.
In embodiment independently, DR detector 190 comprises battery 84 at least one plate that power supply is provided.This embodiment uses a plurality of Switching Power Supplies 200, and each Switching Power Supply all has inducer 70a, the 70b of two alignment, and inducer 70a, 70b are configured to straight line, extend on the V direction and along near signal conductor 78 alignment.It should be noted that the inducer 70a, the 70b that are used for different electrical power 200 are along aliging with the orthogonal H direction of main traverse line direction V.On the contrary as before with reference to as described in Figure 11, every couple of inducer 70a, 70b and nearby inductor make each inducer to not lining up each other to staggered.This helps to minimize when using a plurality of power supply 200 any possible cross-couplings in spot between adjacent paired inducer.
As shown in Figure 9, still there is a certain amount of residual induction noise emf on the lead of nearby inductor 70a and 70b
Res108c.Even, have some image acquisition operations responsive especially to switching transient according to the noise that reduces.In order to help to alleviate the on and off switch transient effect on the induction of signal circuit, can adjust the sequential of on and off switch and phase shift with respect to the signals collecting sequential.
The sequential chart of Figure 13 has shown and the relevant waveform of correlated-double-sampling image acquisition that is used for each pixel column.Component labelling is the block diagram of Fig. 3.Pulse 210 has defined the readout interval 212 of reading all row in the delegation.Be closed generation clamp pulse 214 in the time of charging at switch 66 with sampling capacitor 62.After integration interval 222, produce charging pulse 224 and sampling capacitor 64 chargings, storage is from the integrated signal of charge amplifier.ADC clock 226 is used for the sequential of A/D converter 28.Clock 226 is synchronous with master clock 230 (Fig. 7).The waveform of Figure 13 has represented how a photodiode point works.But be to be understood that and shown in Figure 13 operate in that all the photodiode points to given row synchronously take place during the read operation.
Figure 14 and 15 seems more near the sequential of integration interval among Figure 13 222, how shows phase shift with respect to power supply sequential and current waveform 94,96 work.Figure 14 shows traditional sequential of not using phase shift.Saltus step 223,225 expression capacitors 58 (Fig. 3) charge to the finite integral time of the signal level that is used for pixel.Saltus step 223,225 points out that signal acquisition process especially is subject to two times moment of switching transient influence.Waveform 96,94 has shown inductor current and the switch clock that is used for power supply 200 respectively.Figure 14 has shown the configuration that 200 switch times of power supply and saltus step 223,225 are corresponding to.Because this sequential, induced noise signal tend to produce pseudo-shadow in view data.
Small sequential adjustment helps to compensate this difficulty.Figure 15 has shown result and the advantage thereof that the phase place in the preferred embodiment is adjusted.Herein, switching waveform 94 departs from the sampling saltus step, and its switching signal fully is offset is enough to move its saltus step by saltus step 223,225.With reference to the sketch map of figure 7, order inlet that the sequential phasing is provided to control logic processor 120 by the operator.
By checking view data during fabrication, can determine the optimal location phase position from the radiographic images detector with operating.The clock and the master clock 230 of all switched-mode power supplies that is used for radiographic detector is synchronous, and these master clock 230 control row reading circuits also make capable reading circuit synchronous.Yet the position phase relation of each switched-mode power supply can be adjusted to unique phase deviation position separately.In order to minimize the pseudo-shadow of target image, the ability of this feature and adjustment phase position able to programme provides high degree of flexibility to adjust the operation of each Switching Power Supply in the radiographic detector.
Method of the present utility model helps to reduce the influence of noise in radiographic detector that Switching Power Supply is brought, especially the noise that produces owing to the magnetic field fluctuation when switchable inductor is used as energy-storage travelling wave tube.By using placed in-line two inducers, and align with the row sense wire on the position and be connected with reversed polarity, make switching current reverse flow mistake in each inducer at any time, apparatus and method of the present utility model provide opposite electromagnetic field to make it to cancel out each other along the path of adjacent signal line.Use method and apparatus of the present utility model, can minimize the induction emf effect that switchable inductor is brought, reduced shielding requirements.The holding wire of radiographic images detector and some image acquisition element can be placed or distribution near source element.
Apparatus and method of the present utility model provide portable DR detector flat board, do not need the line of any kind or cable to connect to come work.Wave point 40 (Figure 12) can use many different wireless protocols and in the mechanism any, comprises IEEE 802.11g or IEEE802.11n and other interface facility.Battery 84 can charge repeatedly, and for example lithium ion battery or other sources make the DR detector can work a few hours before needs charge again or change battery.Alternatively, described with reference to figure 7, power supply can be provided by outside DC source 44, for example uses wire cable.In other embodiments, selectively use wired connection or radio configuration, disconnection is connected to be operated on the battery with wire cable.Band wire or radio configuration are selectable, to adapt to the power requirement of the radiographic images that obtains particular type.The requirement of radio communication has been eliminated or replenished to transmission of data signals when the wire cable method also allows transmission voltage.For example in the wire cable method, provide standard USB or Ethernet data to connect and the DC power supply.
Shown in figure 7 and 13-15, embodiment of the present utility model allows to come with respect to the data acquisition function sequential the various selections of gauge tap power supply sequential.This control be programmable, can dynamically adjust or operator's may command or recoverable.For example, as the discussion of reference Figure 15, correction sequence can be used for adjusting timing off-set to obtain minimum measurement noise level.Proofreading and correct to adjust to use technical staff's known method of being familiar with electronic applications manually or by software instruction to realize.
This utility model is described in concrete reference wherein some preferred embodiment in detail, but be to be understood that, the variation and the modification of the scope that shows in above-mentioned spirit of the present utility model and in appended claim are still resultful, for a person skilled in the art, these variations and modification do not break away from this utility model scope.For example, can use the inducer package arrangements different with the configuration shown in Fig. 5 A-6B.Although this description has mainly been set forth the Switching Power Supply design and use in the DR detector, device of the present utility model can use with induction of signal or the blood processor with the use on-board switching power supply of other types easily.Switching Power Supply itself can be comprise blood pressure lowering, boost, oppositely, in push-and-pull, chopper circuit (Cuk) and other the many types any.
Therefore, this paper provides a kind of switching power unit and method that is used to be disposed for digital image detector or other induction electronic installations.
The element tabulation
10. image sensor array
12. photoelectric sensor
14. pixel
15. scintillation screen
16. switch element
18. gate drivers array
20. line
22. sense wire
24. lead
26. amplifier
28.A/D converter
30. bus
32. multiplexer
34. bias generator
40. wave point
44.DC source
50. gate drivers
52. driver line
54. distribution capacity and resistance
56. switch
58. capacitor
60.CDS circuit
62,64. capacitors
66,68. switches
70,70a, 70b. inducer
72. coil
74. magnetic field
78. lead
80. ON-OFF control circuit
82a, 82b. power transistor
84. battery
86. capacitor
88. diode
90. capacitor
92. load
94,96,96a, 96b. waveform
98,98a, 98b. electric current
100. power supply
102a, 102b. electric current
104a, 104b. flux field
106a, 106b. waveform
108a, 108b, 108c. waveform
110a, 110b. inducer are right
120. control logic processor
190.DR detector
200. power supply
210. pulse
212. at interval
214. pulse
222. at interval
223,225. saltus steps
224. pulse
226. clock
230. waveform, master clock
E. amplification profile
H. level
V. vertical
Claims (10)
1. digital radiography detector comprises:
Press the 2 D photoelectric inductor array that row and column is placed;
Many signal conductor connect described photoelectric sensor and extend at first direction along described two-dimensional array; And
Switching Power Supply is connected to power supply and comprises the first and second store electricity sensors, and the wherein said first and second store electricity sensors mate substantially, and electrically series connection comprises the flux field that phase place is opposite, and basically along the described first direction alignment of described signal conductor.
2. digital radiography detector as claimed in claim 1, further comprise the second switch power supply that is connected to described power supply, and comprise the third and fourth store electricity sensor, the wherein said third and fourth store electricity sensor mates basically, electrically series connection, comprise the flux field that phase place is opposite, and basically along the described first direction alignment of described signal conductor.
3. digital radiography detector as claimed in claim 2, wherein said first and second store electricity sensors and the described third and fourth store electricity sensor are staggered.
4. digital radiography detector as claimed in claim 2, wherein the first and second store electricity sensors separate fully with the described third and fourth store electricity sensor, make the described magnetic field of the described first and second store electricity sensors and the described magnetic field non-interference of the described third and fourth store electricity sensor.
5. digital radiography detector as claimed in claim 1, wherein said power supply are the rechargeable batteries that is placed on the described digital radiography detector.
6. digital radiography detector as claimed in claim 1, wherein said power supply is wiredly connected to described detector by cable.
7. digital radiography detector as claimed in claim 1 further comprises wireless data interface.
8. digital radiography detector as claimed in claim 1 further comprises processor, and described processor is configured to drive the adjustable timing off-set between the signal and the sequential of sampled signal for described photoelectric sensor array provides Switching Power Supply.
9. digital radiography detector as claimed in claim 1, wherein said Switching Power Supply be blood pressure lowering, boost, oppositely, in copped wave or the push-pull type power supply one.
10. digital radiography detector as claimed in claim 1, wherein said Switching Power Supply is synchronized with the master clock that is used for reading circuit.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN2009201791940U CN201551320U (en) | 2009-09-28 | 2009-09-28 | Power supply used for portable radiographic detector |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN2009201791940U CN201551320U (en) | 2009-09-28 | 2009-09-28 | Power supply used for portable radiographic detector |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN201551320U true CN201551320U (en) | 2010-08-18 |
Family
ID=42610993
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN2009201791940U Expired - Lifetime CN201551320U (en) | 2009-09-28 | 2009-09-28 | Power supply used for portable radiographic detector |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN201551320U (en) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101556330B (en) * | 2008-04-08 | 2012-07-04 | 卡尔斯特里姆保健公司 | Power supply for portable radiographic detector |
| CN103037608A (en) * | 2011-08-31 | 2013-04-10 | 通用电气公司 | Electron beam manipulation system and method in x-ray sources |
| CN103906333A (en) * | 2012-12-28 | 2014-07-02 | 台达电子工业股份有限公司 | X light pipe power supply device, power supply system with X light pipe power supply device, and operation method of power supply system |
-
2009
- 2009-09-28 CN CN2009201791940U patent/CN201551320U/en not_active Expired - Lifetime
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101556330B (en) * | 2008-04-08 | 2012-07-04 | 卡尔斯特里姆保健公司 | Power supply for portable radiographic detector |
| CN103037608A (en) * | 2011-08-31 | 2013-04-10 | 通用电气公司 | Electron beam manipulation system and method in x-ray sources |
| CN103906333A (en) * | 2012-12-28 | 2014-07-02 | 台达电子工业股份有限公司 | X light pipe power supply device, power supply system with X light pipe power supply device, and operation method of power supply system |
| CN103906333B (en) * | 2012-12-28 | 2016-08-03 | 台达电子工业股份有限公司 | X-ray tube supply unit, the power-supply system with this device and operational approach thereof |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN101556330B (en) | Power supply for portable radiographic detector | |
| CN105556949B (en) | Digital radiography detector image readout | |
| JP2945480B2 (en) | Electrocardiogram sensor device | |
| JP5764468B2 (en) | Radiographic image detection apparatus and radiographic imaging system | |
| US20190109498A1 (en) | Wireless Power Transfer System and Method | |
| EP1966996B1 (en) | Event detection for digital radiography detector | |
| CN105745918B (en) | Digital radiography detector image read-out system and process | |
| US8399846B2 (en) | Radiation image detecting system | |
| US20040021455A1 (en) | Apparatus and method for monitoring power and current flow | |
| CN201551320U (en) | Power supply used for portable radiographic detector | |
| US8774353B2 (en) | Radiation detector with an array of electrodes | |
| CN104983438A (en) | Detector head proximity sensing and collision avoidance apparatuses and methods | |
| JP2004173907A (en) | X-ray radiographing device | |
| JP2010121944A (en) | Transportable-type radiation image photographing apparatus and radiological image photographing system | |
| CN104221270A (en) | Medical imaging device | |
| CN107174247A (en) | Circuit arrangement, MR imaging apparatus and its operation method | |
| JP2005147822A (en) | X-ray image imaging apparatus | |
| JP5171438B2 (en) | Radiography equipment | |
| CN209878912U (en) | Grounding grid signal detection system | |
| JP2012152477A (en) | Radiation imaging system and radiation imaging apparatus | |
| JP5645651B2 (en) | Radiation detection apparatus and radiography system | |
| US20090078878A1 (en) | Radiation imaging cassette | |
| JP5595940B2 (en) | Radiation imaging equipment | |
| JP2007222475A (en) | Electrocardiographic device and mri system | |
| CN110243845A (en) | Radiological image detection |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| AV01 | Patent right actively abandoned |
Granted publication date: 20100818 Effective date of abandoning: 20090928 |