CN100382758C - X ray CT apparatus and projection data collector - Google Patents
X ray CT apparatus and projection data collector Download PDFInfo
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- CN100382758C CN100382758C CNB2004100420184A CN200410042018A CN100382758C CN 100382758 C CN100382758 C CN 100382758C CN B2004100420184 A CNB2004100420184 A CN B2004100420184A CN 200410042018 A CN200410042018 A CN 200410042018A CN 100382758 C CN100382758 C CN 100382758C
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Abstract
The present invention relates to an X-ray CT device and a projection data collection device, wherein the spatial decomposition capacity of a reconstructed image of the X-ray CT device can not be lowered because of reducing two kinds of FOV, and the projection data collection device is used for the X-ray device. The X-ray CT device comprises a multi-channel X-ray detector (24) and a signal collection circuit (26), wherein the channel pitch length of the multi-channel X-ray detector (24) corresponding to the small one of two kinds of a large FOV and a small FOV is 1/n (n is an integral number more than 2) of the external channel pitch length of the multi-channel X-ray detector (24); when the X-ray CT device shoots by the small FOV, the signal collection circuit (26) collects the detection signals from the part corresponding to the small FOV of the X-ray detector according to all the channels; when the X-ray CT device shoots by the large FOV, the signal collection circuit (26) gathers and collects the detection signals from the part corresponding to the small FOV of the X-ray detector according to all the adjacent n channels; simultaneously, the X-ray CT device collects the detection signals from the rest part of the X-ray detector according to all the channels.
Description
Technical field
The present invention relates to X ray CT (Computed Tomography) device and data for projection (data) gathering-device, relate in particular to by X ray and scan (scan) object, reconstruct the X ray CT device of image and be used for the projection data collector of this X ray CT device based on this data for projection so that collect data for projection.
Background technology
In X ray CT device, object is scanned (scan), collecting data for projection (data), and carry out image based on this data for projection and reconstruct.In the collection of data for projection, preestablishing the photography visual field is FOV (field of view), carries out the collection of the data for projection corresponding with this FOV.By in the X-ray detector of multichannel (multi-channel), collect the dateout of the channel of the scope belong to corresponding with FOV, carry out the data collection corresponding with FOV (such as, with reference to patent documentation 1).
[patent documentation 1] spy opens 2001-120534 communique (5-10 page or leaf, Fig. 2-9)
Summary of the invention
The problem that the invention quasi-solution is determined
Because in above-mentioned X ray CT device, FOV is more little, the number of channel that belongs to this scope just reduces more, thereby FOV is more little, and the spatial decomposition ability that makes matrix size (matrix size) reconstruct image when having reached fixedly just reduces more.
Problem of the present invention for this reason is to realize that a kind of spatial decomposition ability that reconstructs image does not reduce X ray CT device that reduces and the projection data collector that is used for this X ray CT because of FOV.
Be used to solve the means of problem
(1) invention that is used to solve a viewpoint of above-mentioned problem is a kind of X ray CT device, be have by X ray come sweep object in case collect data for projection collector unit, reconstruct the unitary X ray CT device of reconstructing of image based on data for projection, it is characterized in that: above-mentioned collector unit possesses the multichannel X-ray detector, wherein with the channel pitch of 2 kinds of medium and small FOV counterparts of FOV of the size of the predesignating 1/n (n is the integer more than 2) for the channel pitch of the part suitable with the non-repeating part of big FOV and little FOV; The signal collection circuit, it is with the photography of little FOV the time, collect detection signal with the little FOV counterpart of above-mentioned X-ray detector by each channel, with the photography of big FOV the time, the detection signal that gathers the little FOV counterpart of collection and above-mentioned X-ray detector by each adjacent n channel, collect the detection signal of the part suitable simultaneously by each channel, collect the detection signal of equal number thus regardless of the size of FOV with the non-repeating part of big FOV and little FOV.
(2) invention that is used to solve another viewpoint of above-mentioned problem is a kind of projection data collector, be to be used for coming sweep object so that collect data for projection by X ray, and reconstruct the projection data collector of the X ray CT device of image based on this data for projection, it is characterized in that: possess the multichannel X-ray detector, wherein with the channel pitch of 2 kinds of medium and small FOV counterparts of FOV of the size of predesignating 1/n (n is the integer more than 2) for the channel pitch of the part suitable with the non-repeating part of big FOV and little FOV; The signal collection circuit, it is with the photography of little FOV the time, collect detection signal with the little FOV counterpart of above-mentioned X-ray detector by each channel, with the photography of big FOV the time, the detection signal that gathers the little FOV counterpart of collection and above-mentioned X-ray detector by each adjacent n channel, collect the detection signal of the part suitable simultaneously by each channel, collect the detection signal of equal number thus regardless of the size of FOV with the non-repeating part of big FOV and little FOV.
The part corresponding with above-mentioned little FOV is present in the central part of above-mentioned X-ray detector, and this is suitable for suitably carrying out the photography this point based on little FOV.The part suitable with the non-repeating part of above-mentioned big FOV and little FOV is present in the both sides with above-mentioned little FOV counterpart, and this is suitable for suitably carrying out the photography this point based on big FOV.N=2 this be suitable for making the size of little FOV to reach half this point of big FOV size.With the number of channel of above-mentioned little FOV counterpart be 2 times of the number of channel of in addition part, this is suitable for making the channel of 2 FOV of size to reach the equal number this point.
The invention effect
In invention with above-mentioned each viewpoint, owing to possess the multichannel X-ray detector, wherein with the channel pitch of 2 kinds of medium and small FOV counterparts of FOV of the size of predesignating 1/n (n is the integer more than 2) for the channel pitch of the part suitable with the non-repeating part of big FOV and little FOV; The signal collection circuit, it is with the photography of little FOV the time, collect detection signal with the little FOV counterpart of above-mentioned X-ray detector by each channel, with the photography of big FOV the time, the detection signal that gathers the little FOV counterpart of collection and above-mentioned X-ray detector by each adjacent n channel, collect the detection signal of the part suitable simultaneously with the non-repeating part of big FOV and little FOV by each channel, collect the detection signal of equal number thus regardless of the size of FOV, thereby can adapt to the minimizing of FOV, reduce the channel pitch of data collection.Therefore, even reduce FOV, the spatial decomposition ability that reconstructs image does not reduce yet.
Description of drawings
Fig. 1 is the block diagram of X ray CT device.
Fig. 2 is the accompanying drawing of the structure of expression X-ray detector.
Fig. 3 is the block diagram of the electric structure of the part be made up of X-ray detector and data collection portion of expression.
Fig. 4 is the block diagram of a kind of state that switch switches in the part of representing to be made up of X-ray detector and data collection portion.
Fig. 5 is the block diagram of a kind of state that switch switches in the part of representing to be made up of X-ray detector and data collection portion.
Fig. 6 is the block diagram of other state that switch switches in the part of representing to be made up of X-ray detector and data collection portion.
Fig. 7 is the block diagram of other state that switch switches in the part of representing to be made up of X-ray detector and data collection portion.
Fig. 8 is the accompanying drawing of the structure of expression x-ray bombardment checkout gear.
Fig. 9 is the accompanying drawing of the relation of expression x-ray bombardment checkout gear and object.
Figure 10 is the flow chart of the action of expression X ray CT device.
Symbol description
2 gantrys; 4 photography platforms; 6 operating consoles; The 20X ray tube; The 24X ray detector; 26 data collection portions; 262,264 change-over switches; 266 signal conditioners
The specific embodiment
Following with reference to accompanying drawing, the best mode that is used to carry out an invention is explained.The present invention is defined in the best mode that is used to carry out an invention in addition.Fig. 1 represents square frame (block) figure of X ray CT device.This device is to be used to implement best mode one example of the present invention.By constituting of this device, represent to be used to implement best mode of the present invention one example of relevant X ray CT device.
As shown in Figure 1, this device has gantry (gantry) 2, photography platform (table) 4 and operating console (console) 6.Gantry 2 has X-ray tube 20.Being shaped by collimator (collimator) 22 from the not shown X ray of X-ray tube 20 radiation, (collimation: collimation), thereby becoming taper (cone) X-ray beam is cone-beam (cone beam) X ray, and shines X-ray detector 24.X-ray detector 24 is according to the diffusion of X-ray beam, and has a plurality of detecting elements that are configured to array (array) shape.Formation to X-ray detector 24 explains later again.
Photography target is equipped on photography platform 4, is sent to the space between X-ray tube 20 and the X-ray detector 24.X-ray tube 20, collimator 22 and X-ray detector 24 constitute the x-ray bombardment checkout gear.To the x-ray bombardment checkout gear, explain again later.
In X-ray detector 24, connect data collection unit 26.Data collection portion 26 is collected the detection signal of each detecting element of X-ray detector 24 as numerical data (digital data).The detection signal of detecting element becomes the signal of expression based on the object projection of X ray.Below, it is also referred to as data for projection or abbreviates data as.
Irradiation from the X ray of X-ray tube 20 is controlled by X ray controller (controller) 28.Omit diagram for the X-ray tube 20 and the annexation of X ray controller 28 in addition.Collimator 22 is controlled by collimator controller 30.Omit diagram for the collimator 22 and the annexation of collimator controller 30 in addition.
This part till from above-mentioned X-ray tube 20 to collimator controller 30 is equipped on the rotating part 34 of gantry 2.The rotation of rotating part 34 is controlled by Rotation Controllers 36.In addition the rotating part 34 and the annexation of Rotation Controllers 36 are omitted diagram.
Gantry 2 is to be used to implement best mode one example of the present invention.By constituting of this device, represent to be used to implement best mode of the present invention one example of relevant projection data collector.
In data processing equipment 60, connect data collection buffer 64.The data collection portion 26 that in data collection buffer 64, connects gantry 2.The data of being collected by data collection portion 26 are input to data processing equipment 60 by data collection buffer 64.
In data processing equipment 60, connect storage device 66.Storage is input to the data for projection of data processing equipment 60 respectively in the storage device 66 by data collection buffer 64 and control interface 62.Also store the program (program) of data processing equipment 60 usefulness in the storage device 66.Data processing equipment 60 is carried out this program, implements the action of this device thus.
In data processing equipment 60, connect display device 68 and operating means 70.Display device 68 is waited by pictorial displays (graphic display) and constitutes.Operating means 70 is waited by the keyboard (keyboard) that possesses indicating device (pointing device) and constitutes.
Fig. 2 represents that the pattern of X-ray detector 24 constitutes.X-ray detector 24 is examples of X-ray detector among the present invention.Shown in figure, X-ray detector 24 is a kind of multichannel (channel) X-ray detectors that a plurality of x-ray detection devices 24 (ik) are configured to 2 dimension array-likes.A plurality of x-ray detection devices 24 (ik) form a kind of X ray sensitive surface that bends to the cylinder concave shape on the whole.
I is a channel designator, such as i=1, and 2 ..., 1500.K is the row sequence numbers, such as k=1, and 2 ..., 32.X-ray detection device 24 (ik) constitutes the detecting element row respectively by row sequence number k components identical.The detecting element row of X-ray detector 24 are not limited to 32 row, also can be majority or the odd numbers that suits.
X-ray detection device 24 (ik) is made of the combination such as flasher (scintillator) and photodiode (photo diode).Be not limited to this in addition, also can be such as the quasiconductor x-ray detection device that has utilized cadmium tellurium (CdTe) etc. or utilized the ionization box x-ray detection device of xenon (Xe) gas.
At the central part of X-ray detector 24, in the prescribed limit of i direction, in addition the i direction size of x-ray detection device 24 (ik) sensitive surface becomes half of x-ray detection device 24 (ik) sensitive surface of part.Like this, the channel pitch of this part (channel pitch) become other parts the channel pitch 1/2.In addition, the channel pitch is not limited to 1/2, when the integer that n is made as more than 2, also can be 1/n.Though below represent the example of n=2, for the integer occasion more than 2, also can be with 2 integers that change into more than it.
Prescribed limit be equivalent to X-ray detector 24 i direction total length about 1/2.This scope is corresponding to the FOV of a less side among 2 kinds of FOV of the size of predesignating.Relative therewith, the i direction length range of X-ray detector 24 is corresponding to a bigger side's FOV.Below, a less side's FOV is also referred to as little FOV, FOV that will a bigger side is called big FOV.
Fig. 3 is represented that by block diagram the electricity of the part be made up of X-ray detector 24 and data collection portion 26 constitutes.Though represented 1 in a plurality of detecting element row here, the formation of relevant other row too.In addition for fear of any confusion, the i direction number of channel of X-ray detector 24 is assumed to be 30.To each channel-attach sequence number 1-30.These 30 channels are corresponding with big FOV.Wherein the channel 6-25 of central part is corresponding with little FOV.The number of channel of little FOV is 20.The pitch of the channel 6-25 of little FOV is 1/2 of the channel 1-5 of big FOV and 26-30.
The output signal of each channel by the change-over switch (switch) 262,264 of 2 systems, is input to signal conditioner (signal conditioner) 266 in data collection portion 26.Signal conditioner 266 is held 20 input channels, to being input to the signal of these channels, and the Signal Regulation that amplify respectively and analog digital (analog-to-digital) conversion etc. suits.To each input channel append serial numbers 1-20.The part of being made up of change-over switch 262,264 and signal conditioner 266 is an example of signal collection circuit among the present invention.
Change-over switch 262 is made up of 20 switch elements corresponding with channel 6-25.Each switch element outputs to the output signal of each channel any one party of 2 signal pathways selectively.One side of 2 signal pathways is general between adjacent 2 switch elements.The switching of each switch element is by carrying out from the control signal of control interface 62.
Change-over switch 264 is made up of 20 switch elements corresponding with the input channel of signal conditioner 266.Each switch element is taken into the input signal of each channel selectively from any one party of 2 signal pathways.The switching of each switch element is by carrying out from the control signal of control interface 62.
Side at 1,2 input signal pathway of input channel is the signal output pathway of the channel 1 of X-ray detector 24, and the opposing party is the side that 2 signals of the switch of channel 6 are exported pathways.Side at 2,2 input signal pathways of input channel is the signal output pathway of the channel 2 of X-ray detector 24, and the opposing party is the side that 2 signals of the switch of channel 7 are exported pathways.Side at 3,2 input signal pathways of input channel is the signal output pathway of the channel 3 of X-ray detector 24, and the opposing party is the side that 2 signals of the switch of channel 8 are exported pathways.Side at 4,2 input signal pathways of input channel is the signal output pathway of the channel 4 of X-ray detector 24, and the opposing party is the side that 2 signals of the switch of channel 9 are exported pathways.Side at 5,2 input signal pathways of input channel is the signal output pathway of the channel 5 of X-ray detector 24, and the opposing party is the side that 2 signals of the switch of channel 10 are exported pathways.
Are general output pathways of switch of the channel 6,7 of X-ray detector 24 a side of 6,2 input signal pathways of input channel, the opposing party is the side of 2 signals output pathways of the switch of channel 11.Are general output pathways of switch of the channel 8,9 of X-ray detector 24 a side of 7,2 input signal pathways of input channel, the opposing party is the side of 2 signals output pathways of the switch of channel 12.Are general output pathways of switch of the channel 10,11 of X-ray detector 24 a side of 8,2 input signal pathways of input channel, the opposing party is the side of 2 signals output pathways of the switch of channel 13.Are general output pathways of switch of the channel 12,13 of X-ray detector 24 a side of 9,2 input signal pathways of input channel, the opposing party is the side of 2 signals output pathways of the switch of channel 14.In the input channel 10, a side of 2 input signal pathways is general output pathways of switch of the channel 14,15 of X-ray detector 24, and the opposing party is the side of 2 signals output pathways of the switch of channel 15.
Are general output pathways of switch of the channel 16,17 of X-ray detector 24 a side of 11,2 input signal pathways of input channel, the opposing party is the side of 2 signals output pathways of the switch of channel 16.Are general output pathways of switch of the channel 18,19 of X-ray detector 24 a side of 12,2 input signal pathways of input channel, the opposing party is the side of 2 signals output pathways of the switch of channel 17.Are general output pathways of switch of the channel 20,21 of X-ray detector 24 a side of 13,2 input signal pathways of input channel, the opposing party is the side of 2 signals output pathways of the switch of channel 18.Side at 14,2 input signal pathways of input channel is the general output pathway of channel 22,23 switches of X-ray detector 24, and the opposing party is the side that 2 signals of the switch of channel 19 are exported pathways.Are general output pathways of switch of the channel 24,25 of X-ray detector 24 a side of 15,2 input signal pathways of input channel, the opposing party is the side of 2 signals output pathways of the switch of channel 20.
Side at 16,2 input signal pathways of input channel is the signal output pathway of the channel 26 of X-ray detector 24, and the opposing party is the side that 2 signals of the switch of channel 21 are exported pathways.Side at 17,2 input signal pathways of input channel is the signal output pathway of the channel 27 of X-ray detector 24, and the opposing party is the side that 2 signals of the switch of channel 22 are exported pathways.Side at 18,2 input signal pathways of input channel is the signal output pathway of the channel 28 of X-ray detector 24, and the opposing party is the side that 2 signals of the switch of channel 23 are exported pathways.Side at 19,2 input signal pathways of input channel is the signal output pathway of the channel 29 of X-ray detector 24, and the opposing party is the side that 2 signals of the switch of channel 24 are exported pathways.Side at 20,2 input signal pathways of input channel is the signal output pathway of the channel 30 of X-ray detector 24, and the opposing party is the side that 2 signals of the switch of channel 25 are exported pathways.
Fig. 4 represents the switching state of one of change-over switch 262,264.Shown in figure, at this state, change-over switch 262 is switched to: to channel 6-25, by per 2 adjacent channels, these output signals are outputed to general signal pathway.Like this, channel 6 and 7,8 and 9,10 and 11,12 and 13,14 and 15,16 and 17,18 and 19,20 and 21,22 and 23,24 and 25 output signal are outputed to general signal pathway by parallel respectively.
Change-over switch 264 is switched to: the output signal of the channel 1-5 of X-ray detector 24 and 26-30 is input to the channel 1-5 and the 16-20 of signal conditioner 266 respectively, is switched in addition: with the channel 6 of X-ray detector 24 and 7 parallel output signal, 8 and 9 parallel output signal, 10 and 11 parallel output signal, 12 and 13 parallel output signal, 14 and 15 parallel output signal, 16 and 17 parallel output signal, 18 and 19 parallel output signal, 20 and 21 parallel output signal, 22 and 23 parallel output signal, 24 and 25 parallel output signal is input to the channel 6-15 of signal conditioner 266 respectively.
If only represent active (active) signal pathway under this state, just as shown in Figure 5, the output signal that belongs to all channel 1-30 of big FOV is imported into signal conditioner 266.The output signal that belongs to the channel 6-25 of little FOV this moment is gathered input by every 2 adjacent next quilts.
Like this, channel 6 and 7,8 and 9,10 and 11,12 and 13,14 and 15,16 and 17,18 and 19,20 and 21,22 and 23,24 and 25 is brought into play function as 1 channel respectively.Therefore, X-ray detector 24 is brought into play function as the X-ray detector of 20 channels, and it is impartial that substantial channel pitch reaches in the FOV entire scope.
Fig. 6 represents other switching state of change-over switch 262,264.Shown in figure, at this state, change-over switch 262 is switched to: the output signal of channel 6-25 is outputed to one signal pathway.Change-over switch 264 is switched in addition: the channel 1-20 that the output signal of channel 6-25 is input to signal conditioner 266 respectively.
If only represent the active signal pathway under this state, just as shown in Figure 7, the output signal that only belongs to the channel 6-25 of little FOV is imported into signal conditioner 266.Like this, X-ray detector 24 is same with the occasion of big FOV, brings into play function as the X-ray detector of 20 channels, but owing to only use channel 6-25, so the channel pitch becomes 1/2 of big FOV occasion.Therefore, can collect data with the occasion equal number of big FOV by 2 times spatial decomposition ability.
Fig. 8 represents the mutual relation of X-ray tube in the x-ray bombardment checkout gear 20 and collimator 22 and X-ray detector 24.Fig. 8 (a) is the accompanying drawing of the expression state of looking from the front of gantry 2 in addition, (b) is the accompanying drawing of representing the state of looking from the side.Shown in figure, the X ray that radiates from X-ray tube 20 is configured as: become cone-shaped X-ray beam 400 by collimator 22, and shine X-ray detector 24.
Dispersing of a direction of the cone-shaped X-ray beam 400 of Fig. 8 (a) expression.Below, also this direction is called the amplitude direction.The amplitude direction of X-ray beam 400 is consistent with the configuration direction of channel in the X-ray detector 24.In the divergence range of X-ray beam 400, set big FOV and little FOV.(b) other direction of expression X-ray beam 400 disperses.Below, also this direction is called the thickness direction of X-ray beam 400.In the thickness direction of X-ray beam 400 and the X-ray detector 24 a plurality of detecting elements row and to put direction consistent.It is orthogonal that 2 of X-ray beam 400 disperse direction.
This X-ray beam 400 is intersected with axon, and such as shown in Figure 9, the object 8 of institute's mounting is moved the x-ray bombardment space on the photography platform 4.Gantry 2 is a kind of tubular structures that comprise the x-ray bombardment checkout gear in inside.
The x-ray bombardment space forms at the inner space of the tubular structure of gantry 2.By X-ray beam 400 come layering the image of object 8 be projected to X-ray detector 24.By X-ray detector 24, the X ray that has seen through object 8 is detected by each detector columns.The thickness t h that shines the X-ray beam 400 of object 8 is regulated by the eyelet aperture of collimator 22.
Parallel, as shown in arrow 42 with the rotation of x-ray bombardment checkout gear, photography platform 4 is moved continuously in the axon direction of object 8, the relative thus object 8 of x-ray bombardment checkout gear rotates along the helical track of surrounding object 8.Carry out so-called helical scanning (helical scan) thus.If under the state that photography platform 4 is stopped, making the rotation of x-ray bombardment checkout gear, can carry out axial scan (axial scan).
With the rotating shaft direction of scanning as the z direction, with the direction that connects center of rotation and X-ray tube 20 as the y direction, will with z direction and the vertical direction of y direction as the x direction.Form rotating coordinate system xyz thus.
Every rotation sweep 1 time is just collected the data for projection that repeatedly (such as 1000 times) observe (view).The collection of data for projection is by the X-ray detector 24-data collection 26-of portion data collection buffer 64 these a series of carrying out.
Action to this device is explained.Figure 10 represents flow process (flow) figure of this device action.Shown in figure,, carry out photography conditions and set in step (stage) 501.Photography conditions is set and is undertaken by operating means 70 by user.Set various sweep parameters (scan parameter) such as photography position, FOV, tube voltage, tube current, lift height thus.
Next, scan in step 503.According to the photography conditions of setting in step 501, scan by gantry 2 and photography platform 4.Come the data for projection of intelligence-collecting object 8 thus.
Next, carrying out image in step 507 reconstructs.Image reconstructs by data processing equipment 60 and is undertaken.Data processing equipment 60 is based on by the collected data for projection of scanning, waits and reconstructs image by returning the filter sciagraphy.Reconstituted image is shown and stores in step 509.The demonstration of image is undertaken by display device 60.The storage of image is undertaken by storage device 66.
In above-mentioned photography, big FOV photography is carried out under the connection status of X-ray detector shown in Figure 5 24 and data collection portion 26, and little FOV photography is carried out under the connection status of X-ray detector shown in Figure 7 24 and data collection portion 26.As shown in Figure 7, owing to FOV is being reduced under 1/2 the occasion, corresponding therewith the channel pitch is set to 1/2, collects the data with the occasion equal number of FOV, even thereby FOV reduce, the spatial decomposition ability that reconstructs image does not descend yet.
The relation of 2 FOV of size can be set at a plurality of stages.That is,, can set its FOV greatly,, can set its slight FOV by above-mentioned relation as big FOV to little FOV by above-mentioned relation as little FOV to big FOV.For and too less than the FOV of slight FOV greater than the FOV of FOV greatly.
Claims (10)
1. X ray CT device, be have by X ray come sweep object in case collect data for projection collector unit, reconstruct the unitary X ray CT device of reconstructing of image based on data for projection, it is characterized in that:
Above-mentioned collector unit possesses
The multichannel X-ray detector is the 1/n of channel pitch of the non-repeating part of big FOV and little FOV with the channel pitch of 2 kinds of medium and small FOV counterparts of FOV of the size of predesignating wherein, and wherein n is the integer more than 2;
The signal collection circuit, it is with the photography of little FOV the time, collect detection signal with the little FOV counterpart of above-mentioned X-ray detector by each channel, with the photography of big FOV the time, the detection signal that gathers the little FOV counterpart of collection and above-mentioned X-ray detector by each adjacent n channel, collect the detection signal of the non-repeating part of big FOV and little FOV simultaneously by each channel, collect the detection signal of equal number thus regardless of the size of FOV.
In the claim 1 record X ray CT device, it is characterized in that:
The part corresponding with above-mentioned little FOV is present in the central part of above-mentioned X-ray detector.
In claim 1 or the claim 2 record X ray CT device, it is characterized in that:
The non-repeating part of above-mentioned big FOV and little FOV is present in the both sides with above-mentioned little FOV counterpart.
In the claim 1 record X ray CT device, it is characterized in that:
n＝2。
In the claim 4 record X ray CT device, it is characterized in that:
With the number of channel of above-mentioned little FOV counterpart be 2 times of the number of channel of the non-repeating part of above-mentioned big FOV and little FOV.
6. projection data collector is to be used for coming sweep object so that collect data for projection by X ray, and reconstructs the projection data collector of the X ray CT device of image based on this data for projection, it is characterized in that: possess
The multichannel X-ray detector is the 1/n of channel pitch of the non-repeating part of big FOV and little FOV with the channel pitch of 2 kinds of medium and small FOV counterparts of FOV of the size of predesignating wherein, and wherein n is the integer more than 2;
The signal collection circuit, it is with the photography of little FOV the time, collect detection signal with the little FOV counterpart of above-mentioned X-ray detector by each channel, with the photography of big FOV the time, the detection signal that gathers the little FOV counterpart of collection and above-mentioned X-ray detector by each adjacent n channel, collect the detection signal of the non-repeating part of big FOV and little FOV simultaneously by each channel, collect the detection signal of equal number thus regardless of the size of FOV.
In the claim 6 record projection data collector, it is characterized in that:
The part corresponding with above-mentioned little FOV is present in the central part of above-mentioned X-ray detector.
In claim 6 or the claim 7 record projection data collector, it is characterized in that:
The non-repeating part of above-mentioned big FOV and little FOV is present in the both sides of the part corresponding with above-mentioned little FOV.
In the claim 6 record projection data collector, it is characterized in that:
n＝2。
In the claim 9 record projection data collector, it is characterized in that:
With the number of channel of above-mentioned little FOV counterpart be 2 times of the non-repeating part number of channel of above-mentioned big FOV and little FOV.
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CNB2004100420184A CN100382758C (en) | 2004-04-29 | 2004-04-29 | X ray CT apparatus and projection data collector |
| JP2004372911A JP2005312912A (en) | 2004-04-29 | 2004-12-24 | X-ray ct apparatus and projection data collection equipment |
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| CNB2004100420184A CN100382758C (en) | 2004-04-29 | 2004-04-29 | X ray CT apparatus and projection data collector |
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| CN100382758C true CN100382758C (en) | 2008-04-23 |
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| JP5168415B2 (en) * | 2009-09-16 | 2013-03-21 | コニカミノルタオプティクス株式会社 | Biological information measuring system, method of using biological information measuring apparatus and communication method |
| JP2013198724A (en) * | 2012-02-24 | 2013-10-03 | Toshiba Corp | X-ray ct device and control program thereof |
| CN113520440B (en) * | 2021-07-13 | 2024-04-19 | 深圳安科高技术股份有限公司 | Cardiac CT scanning detection device and cardiac CT scanning reconstruction method |
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| CN1133973A (en) * | 1995-01-27 | 1996-10-23 | 西门子公司 | Computerized laminography camera |
| CN1224603A (en) * | 1997-11-07 | 1999-08-04 | 通用电气公司 | Methods and apparatus for cell ganging in multislice computed tomography system |
| JP2001120534A (en) * | 1999-10-28 | 2001-05-08 | Hitachi Medical Corp | Multislice type x-ray ct apparatus |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| JPS53114378A (en) * | 1977-03-16 | 1978-10-05 | Toshiba Corp | Tomographic pickup unit by radiation |
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Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1133973A (en) * | 1995-01-27 | 1996-10-23 | 西门子公司 | Computerized laminography camera |
| CN1224603A (en) * | 1997-11-07 | 1999-08-04 | 通用电气公司 | Methods and apparatus for cell ganging in multislice computed tomography system |
| JP2001120534A (en) * | 1999-10-28 | 2001-05-08 | Hitachi Medical Corp | Multislice type x-ray ct apparatus |
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| CN1689519A (en) | 2005-11-02 |
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