CN106852697A - Radioscopic image acquisition methods and device - Google Patents
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Abstract
A kind of radioscopic image acquisition methods and device, the acquisition methods include：According to the initial gantry parameter of pre-exposure region setting and the overlapping region of adjacent two field pictures, calculating carries out the initial exposure frame number of image mosaic；Adjust the initial exposure frame number and obtain actual exposure frame number, and practical frame parameter is determined according to the actual exposure frame number, so that actual exposure region is not more than the pre-exposure region, and the actual exposure frame number is less than 1 with the absolute value of the difference of the initial exposure frame number；Based on the actual exposure frame number and the practical frame parameter, corresponding detector position and the bulb anglec of rotation when calculating collection per two field picture；Corresponding detector position and the bulb anglec of rotation are exposed during with the practical frame parameter, collection per two field picture, obtain image to be spliced.Using methods described and device, detected object can be effectively prevented from and receive excessive dose of radiation in photographic process.
Description
The application is to submit Patent Office of the People's Republic of China, Application No. 201410508290.0, invention name on 09 28th, 2014
The referred to as divisional application of the Chinese patent application of " radioscopic image acquisition methods and device ".
Technical field
The present invention relates to technical field of image processing, more particularly to a kind of radioscopic image acquisition methods and device.
Background technology
Using X-ray shooting system, the image film making of large scale, big field range is carried out, such as：Shoot skeletal image, ridge
Post image etc. has become one kind and is widely applied.
For now, due to being limited in physical characteristic by X-ray shooting system, such as area limitation of detector,
Source image away from (SID, Source Image Distance) distance limitation etc., when being imaged to large-sized position to be photographed,
Generally using by large-sized position to be photographed, the size requirement that detector can meet when being divided into individual photography carries out sequence and takes the photograph
Shadow, is then merged to the sequence image that photography is obtained by image workstation, is spliced, is processed, to obtain large-sized shadow
Picture.
But when being photographed to large-sized position to be photographed using aforesaid way, may result in detected object receiving
Excessive dose of radiation, certain injury is produced to it.
The content of the invention
The problem that the embodiment of the present invention is solved is how to avoid detected object from receiving excessive radiation agent in photographic process
Amount.
To solve the above problems, the embodiment of the present invention provides a kind of radioscopic image acquisition methods, including：
According to the initial gantry parameter of pre-exposure region setting and the overlapping region of adjacent two field pictures, calculating carries out image
The initial exposure frame number of splicing；Gantry parameter includes：The height of the original position, final position and effective light field of effective light field
Degree, at least includes two height of effective light field between the original position and final position of effective light field, described to have
The height for imitating light field is related to the openings of sizes of beam-defining clipper on vertical direction；
Adjust the initial exposure frame number and obtain actual exposure frame number, when the initial exposure frame number is integer, the reality
Border exposure frame number is the initial exposure frame number；When the initial exposure frame number is non-integer, the actual exposure frame number association
In the rate of change of image mosaic stroke；
Practical frame parameter is determined according to the actual exposure frame number so that actual exposure region is not more than the pre-exposure
Region, and the actual exposure frame number is less than 1 with the absolute value of the difference of the initial exposure frame number；
Based on the actual exposure frame number and the practical frame parameter, corresponding detector when calculating collection per two field picture
Position and the bulb anglec of rotation；
Corresponding detector position and the bulb anglec of rotation are exposed during with the practical frame parameter, collection per two field picture
Light, obtains image to be spliced.
Optionally, the initial exposure frame number for carrying out image mosaic is calculated by equation below：
Y=(L0-Lp)/(h0-Lp)；
Wherein, Y is initial exposure frame number, LpIt is the overlapping region of adjacent two field pictures, h0It is the height of initial effectively light field
Degree, L0It is initial splicing stroke；
The initial splicing stroke L0Obtained by equation below：
L0=Zstart0-Zstop0；
Wherein, Zstart0It is the original position of initial effectively light field, Zstop0It is the final position of initial effectively light field.
Optionally, the rate of change of described image splicing stroke is obtained by equation below：
P=(L0-L1)/L0；
Wherein, L1It is default splicing stroke, P is the rate of change of image mosaic stroke；
The default splicing stroke L1Obtained by equation below：
L1=floor (Y) × (h0-Lp)+Lp；
Wherein, function floor (x) is to take the maximum integer less than x.
Optionally, when the actual exposure frame number is initial exposure frame number, the practical frame parameter is initial frame
Parameter, described based on the actual exposure frame number and the practical frame parameter, corresponding detection when calculating collection per two field picture
Device position is carried out by equation below：
ZFDn=Zstart0-((2n-1)/2)×h0+(n-1)×Lp；
Wherein, ZFDnCorresponding detector center during for collection n-th frame image, n is exposure frame number；
It is described based on the actual exposure frame number and the practical frame parameter, corresponding ball when calculating collection per two field picture
The pipe anglec of rotation is carried out by equation below：
Wherein, αRHAThe angle of the bulb axis of bulb and X-axis in XZ Plane Rotations during for collection n-th frame image, and adopts
The difference of bulb angle of the axis and X-axis of bulb in XZ Plane Rotations when collecting the (n-1)th two field picture；It is arc tangent letter
Number, SSIDIt is source image away from ZTCSIt is the bulb focus and the distance of ground level, ZnIt is the initial position of n-th frame image；
The initial position Z of the n-th frame imagenObtained by equation below：
Zn=Zstart0-(n-1)×h0+(n-1)×Lp。
Optionally, when the rate of change of described image splicing stroke is less than or equal to predetermined threshold value, the actual exposure frame number is
Less than the maximum integer of the initial exposure frame number.
Optionally, when the actual exposure frame number is less than the maximum integer of the initial exposure frame number, corresponding reality
The height of actually active light field is the height of the initial effectively light field, the original position of actually active light field in gantry parameter
ZstartAnd final position ZstopObtained by equation below respectively：
Zstop=Zstop0+(L0-L1)/2。
Optionally, it is described based on the actual exposure frame number and the practical frame parameter, when calculating collection per two field picture
Corresponding detector position is carried out by equation below：
ZFDn=Zstart-((2n-1)/2)×h0+(n-1)×Lp；
Wherein, ZFDnCorresponding detector center during for collection n-th frame image, n is exposure frame number；
It is described based on the actual exposure frame number and the practical frame parameter, corresponding ball when calculating collection per two field picture
The pipe anglec of rotation is carried out by equation below：
Wherein, αRHAThe angle of the bulb axis of bulb and X-axis in XZ Plane Rotations during for collection n-th frame image, and adopts
The difference of bulb angle of the axis and X-axis of bulb in XZ Plane Rotations when collecting the (n-1)th two field picture；It is arc tangent letter
Number, SSIDIt is source image away from ZTCSIt is the bulb focus and the distance of ground level, ZnIt is the initial position of n-th frame image；
The initial position Z of the n-th frame imagenObtained by equation below：
Zn=Zstart-(n-1)×h0+(n-1)×Lp。
Optionally, when described image splicing stroke rate of change be more than predetermined threshold value, the actual exposure frame number be less than
The maximum integer of the initial exposure frame number adds 1.
Optionally, when the maximum integer that the actual exposure frame number is the initial exposure frame number plus 1, corresponding actual machine
The original position of actually active light field is the original position of initial effectively light field, the final position of actually active light field in frame parameter
It is the final position of initial effectively light field, the height of actually active light field is obtained by equation below：
H=Lp+(L0-Lp)/(floor(Y)+1)。
Optionally, it is described based on the actual exposure frame number and the practical frame parameter, when calculating collection per two field picture
Corresponding detector position is carried out by equation below：
ZFDn=Zstart0-((2n-1)/2)×h+(n-1)×Lp；
Wherein, ZFDnCorresponding detector center during for collection n-th frame image, n is exposure frame number；
It is described based on the actual exposure frame number and the practical frame parameter, corresponding ball when calculating collection per two field picture
The pipe anglec of rotation is carried out by equation below：
Wherein, αRHAThe angle of the bulb axis of bulb and X-axis in XZ Plane Rotations during for collection n-th frame image, and adopts
The difference of bulb angle of the axis and X-axis of bulb in XZ Plane Rotations when collecting the (n-1)th two field picture；It is arc tangent letter
Number, SSIDIt is source image away from ZTCSIt is the bulb focus and the distance of ground level, ZnIt is the initial position of n-th frame image；
The initial position Z of the n-th frame imagenObtained by equation below：
Zn=Zstart0-(n-1)×h+(n-1)×Lp。
To solve the above problems, the embodiment of the present invention additionally provides a kind of radioscopic image acquisition device, including：
First computing unit, for the overlap according to the initial gantry parameter of pre-exposure region setting and adjacent two field pictures
Region, calculating carries out the initial exposure frame number of image mosaic；Gantry parameter includes：Original position, the final position of effective light field
And the height of effective light field, two effective light are at least included between the original position and final position of effective light field
Wild height, the height of effective light field is related to the openings of sizes of beam-defining clipper on vertical direction；
First acquisition unit, obtains actual exposure frame number, when the initial exposure for adjusting the initial exposure frame number
Frame number is integer, and the actual exposure frame number is the initial exposure frame number；It is described when the initial exposure frame number is non-integer
Actual exposure frame number is associated with the rate of change of image mosaic stroke；Practical frame parameter is determined according to the actual exposure frame number,
So that actual exposure region is not more than the pre-exposure region, and the actual exposure frame number and the initial exposure frame number difference
The absolute value of value is less than 1；
Second computing unit, for based on the actual exposure frame number and the practical frame parameter, calculating collection per frame
Corresponding detector position and the bulb anglec of rotation during image；
Image acquisition unit, for the practical frame parameter, collection per two field picture when corresponding detector position and
The bulb anglec of rotation is exposed, and obtains image to be spliced.
Compared with prior art, the technical scheme of the embodiment of the present invention has advantages below：
Initial exposure frame number is obtained according to pre-exposure region, initial exposure frame number is adjusted and is obtained actual exposure frame number
And its corresponding practical frame parameter so that the corresponding actual exposure region of actual exposure frame number is not more than pre-exposure region, and
The absolute value of the difference between actual exposure frame number and initial exposure frame number is less than 1.Such that it is able to avoid in actual clinical, when
When initial exposure frame number is non-integer, only take causes actual exposure more than the integer of initial exposure frame number as actual exposure frame number
Light region is more than pre-exposure region, and then causes detected object to receive excessive dose of radiation, you can to efficiently reduce photography
During detected object receive dose of radiation.The rate of change of image mosaic stroke is associated with due to the actual exposure frame number,
And according to described image splice stroke rate of change and predetermined threshold value between relation, it is determined that final actual exposure frame number and
Its corresponding practical frame parameter, therefore the image for meeting actual clinical demand can be obtained.
Additionally, in photographic process, the height due to bulb in Z-direction is fixed, it rotates in XZ planes, detection
The position of device is then as being rotated in Z-direction for bulb is adjusted correspondingly so that the matter of the sequence image that photography is obtained
Amount can meet actual clinical demand, and then also improve spliced picture quality.
Brief description of the drawings
Fig. 1 is the flow chart of the radioscopic image acquisition methods of the embodiment of the present invention；
Fig. 2 is schematic diagram of the X-ray shooting system at the first moment；
Fig. 3 is schematic diagram of the X-ray shooting system at the second moment；
Fig. 4 is a kind of schematic diagram of determination initial exposure frame number of the embodiment of the present invention；
Fig. 5 be the embodiment of the present invention collection n-th frame image before bulb rotation angle schematic diagram；
Fig. 6 is the structural representation of the radioscopic image acquisition device of the embodiment of the present invention.
Specific embodiment
As described in the background art, prior art may result in detected object and connect when image on a large scale is obtained
By excessive dose of radiation.Inventor has found, in the photographic process for carrying out large scale image, is calculated according to pre-exposure region
After going out the initial exposure frame number of image mosaic, if initial exposure frame number is not integer, doctor would generally be taken more than initial exposure frame
Several integers as the exposure frame number in actual photographic process, therefore, cause actual exposure region be more than pre-exposure region so that
Detected object receives excessive dose of radiation, to which creating certain injury.
Inventor considers, is adjusted correspondingly to obtain actual exposure frame to calculating the initial exposure frame number for obtaining
Number so that actual exposure region is not more than pre-exposure region, such that it is able to reduce the radiation of detected object receiving in photographic process
Dosage.Further, initial exposure frame number is adjusted by the rate of change of image mosaic stroke to obtain actual exposure frame number, and
The corresponding practical frame parameter of actual exposure frame number is obtained, the image of actual clinical demand is met to obtain.
As shown in figure 1, the radioscopic image acquisition methods of the embodiment of the present invention include：
Step S101：According to the initial gantry parameter of pre-exposure region setting and the overlapping region of adjacent two field pictures, meter
Calculation carries out the initial exposure frame number of image mosaic；
Step S102：Adjust the initial exposure frame number and obtain actual exposure frame number, and according to the actual exposure frame number
Determine practical frame parameter so that actual exposure region is not more than the pre-exposure region, and the actual exposure frame number and institute
The absolute value for stating the difference of initial exposure frame number is less than 1；
Step S103：Based on the actual exposure frame number and the practical frame parameter, when calculating collection per two field picture pair
The detector position and the bulb anglec of rotation answered；
Step S104：Corresponding detector position and bulb rotate during with the practical frame parameter, collection per two field picture
Angle is exposed, and obtains image to be spliced.
It is understandable to enable the above-mentioned purpose of the embodiment of the present invention, feature and advantage to become apparent, it is right below in conjunction with the accompanying drawings
Specific embodiment of the invention is described in detail.
Before radioscopic image acquisition methods in the embodiment of the present invention are described in detail, first the present invention is implemented
The structure of the X-ray shooting system that example is used briefly is introduced.
Reference picture 2 and Fig. 3, Fig. 2 are schematic diagram of the X-ray shooting system at the first moment, and Fig. 3 is X-ray shooting system
In the schematic diagram at the second moment.
In Fig. 2 and Fig. 3, X-ray shooting system mainly includes：Crossbeam 1, radiography bed 2, detector 3, column 4, moving guide rail
5th, the suspension arm 6 and bulb 7 (X/Y plane of XYZ three-dimensional system of coordinates is parallel with ground level o1 in Fig. 2 and 3) that can be stretched up and down, its
In：Column 4 is typically fixed on the floor of computer room (face where floor is ground level o1), and detector 3 is provided with thereon,
It is provided with to control beamy beam-defining clipper 11 on bulb 7.
Detector 3 can do oscilaltion campaign along column 4, and bulb 7 is connected by tube stand 8 with suspension arm 6；Bulb branch
Frame 8 can make bulb 7 respectively in X/Y plane and/or XZ Plane Rotations, also be risen up and down together with the suspension arm 6 that can be stretched up and down
Drop motion.Tube stand 8 mainly includes perpendicular first support 80 and second support 81, in Fig. 2, by the center of suspension arm 6
Axle is defined as axle RVA and axle RVA is parallel with Z axis, and the central shaft of second support 81 is defined as axle RHA and axle RHA is parallel with Y-axis.
First support 80 can drive overall tube stand 8 and bulb 7 to be rotated in X/Y plane around axle RVA, and second support 81 makes bulb 7 around axle
RHA is in XZ Plane Rotations.
Step S101 is performed, according to the initial gantry parameter of pre-exposure region setting and the overlay region of adjacent two field pictures
Domain, calculating carries out the initial exposure frame number of image mosaic.
In specific implementation, gantry parameter can include original position, final position and effective light field of effective light field
Height, the height of two effective light fields can be at least included between the original position and final position of effective light field, and effectively
The height of light field is related to the openings of sizes of beam-defining clipper in the vertical direction.In an embodiment of the present invention, the height of effective light field
, equal to the openings of sizes of beam-defining clipper in the vertical direction and the product of constant value k, constant value k can be according to actual clinical demand for degree
Set.
In an embodiment of the present invention, effective light field refers to that what is received on detector can form the light field of effective image
Scope.The original position of effective light field refers to the upper edge of the first two field picture corresponding effective light field when shooting the first two field picture；
The final position of effective light field refers to the lower edge of last frame image corresponding effective light field when shooting last frame image.
In embodiments of the present invention, pre-exposure region can be determined, and then set initial machine according to position to be captured
Frame parameter, i.e., initialize to gantry parameter.Initial gantry parameter includes：The initial effectively original position of light field, it is initial effectively
The height of the final position of light field and initial effectively light field.In practical application, gantry parameter can be entered according to clinical demand
Row initialization, for example, doctor can first determine pre-exposure region according to position to be photographed, is determined initial based on the pre-exposure region
The original position and final position of effective light field, the height of initial effectively light field is determined according to clinical demand.
After setting the initial effectively original position of light field, final position and the initial effectively height of light field, can basis
The initial effectively original position of light field, final position determine the initial splicing stroke of image to be spliced.According to the initial spelling
The overlapping region of adjacent two field pictures in stroke, the height and image to be spliced of initial effectively light field is connect, initial exposure is calculated
Light frame number.
Fig. 4 gives a kind of schematic diagram of the determination initial exposure frame number in the embodiment of the present invention.In Fig. 4, dotted line frame 201
The position of effective light field corresponding with the first two field picture is represented, dotted line frame 20n represents effective light corresponding with last frame image
Wild position.The upper edge of dotted line frame 201 represents the original position of initial effectively light field, and the lower edge of dotted line frame 20n represents just
The final position of effective light field that begins.Solid box 202 represents the position of effective light field corresponding with the second two field picture, and solid box
There is overlapping region between 202 and dotted line frame 201, the length of overlapping region is Lp.Dotted line frame 201,20n and solid box 202
Height be the height h of initial effectively light field0, the expression ground level of straight line 204.
As shown in Figure 4, the original position of initial effectively light field is Z relative to the height value of ground levelstart0, it is initial effective
The final position of light field is Z relative to the height value of ground levelstop0, according to the original position and final position of initial effectively light field
The distance between, the initial splicing stroke L of image to be spliced can be calculated0For：
L0=Zstart0-Zstop0。
According to initial splicing stroke L0And between adjacent two field pictures overlapping region length Lp, calculate initial exposure frame
Counting Y is：
Y=(L0-Lp)/(h0-Lp)。
Step S102 is performed, the initial exposure frame number is adjusted and is obtained actual exposure frame number, and according to the actual exposure
Frame number determines practical frame parameter so that actual exposure region is not more than the pre-exposure region, and the actual exposure frame number
Absolute value with the difference of the initial exposure frame number is less than 1.
In embodiments of the present invention, the initial exposure frame number being calculated in step S101 is probably integer value, it is also possible to
It is non integer value.And in actual applications, finally need the frame number being exposed to should be integer value.When initial exposure frame number is
During integer value, initial exposure frame number can not be adjusted, actual exposure frame number is initial exposure frame number.Work as initial exposure
, it is necessary to be adjusted to initial exposure frame number according to actual clinical demand when frame number is non integer value, to obtain correspondence integer
The actual exposure frame number of value.For example, the integer part of initial exposure frame number can be taken as actual exposure frame number.And for example, can be with
The integer part for taking initial exposure frame number plus 1 as actual exposure frame number.
In an embodiment of the present invention, when initial exposure frame number is non-integer, the acquisition of actual exposure frame number is associated with
The rate of change of image mosaic stroke, the rate of change of image mosaic stroke is then associated with initial splicing stroke L0With default splicing stroke
L1, specifically, calculating the rate of change of image mosaic stroke by equation below：
P=(L0-L1)/L0；
Wherein, P is the rate of change of image mosaic stroke, L0It is initial splicing stroke, L1It is default splicing stroke, it is described pre-
If splicing stroke is：
L1=floor (Y) × (h0-Lp)+Lp；
The implication of function floor (x) is：Take the maximum integer less than x.
After obtaining the rate of change of image mosaic stroke according to above-mentioned formula, by the rate of change of image mosaic stroke with it is default
Threshold value is compared, and actual exposure frame number is determined according to comparative result.
In an embodiment of the present invention, when the rate of change of image mosaic stroke is less than or equal to predetermined threshold value, then it represents that no
The length for being enough to expose a frame is little to the final image contributions for splice, gives up the fractional part of initial exposure frame number, i.e., with
Floor (Y) also complies with actual clinical demand as actual exposure frame number, the final stitching image for obtaining；And work as image mosaic
When the rate of change of stroke is more than predetermined threshold value, then it represents that be not enough to expose the length of a frame to the final image contributions for having spliced compared with
Greatly, it is impossible to give up the fractional part of initial exposure frame number, i.e., using floor (Y)+1 as actual exposure frame number.
In embodiments of the present invention, the scope of the predetermined threshold value is [3%, 7%].Specifically, the predetermined threshold value can
Think：5%, in other embodiments, the predetermined threshold value can also be：6% or 7%.Doctor can facing according to its reality
Bed demand is set accordingly to the predetermined threshold value.
In the embodiment of the present invention, when initial exposure frame number is integer, actual exposure frame number is identical with initial exposure frame number,
Now, it is not necessary to be adjusted to initial gantry parameter, gantry parameter that also will be initial is used as practical frame parameter.Originally
When beginning exposure frame number for non-integer, then need to be adjusted initial gantry parameter, to determine practical frame parameter, to meet
Can obtain and meet the image of actual clinical demand and can reduce the dose of radiation that patient receives again.
It is right individually below as noted previously, as actual exposure frame number may be floor (Y), it is also possible to be floor (Y)+1
When actual exposure frame number takes different value, the value of corresponding practical frame parameter is illustrated accordingly.
1) if actual exposure frame number is floor (Y), for initial exposure frame number, actual exposure frame number is less than
Initial exposure frame number, corresponding actual splicing stroke is
L1=floor (Y) × (h0-Lp)+Lp。
For initial splicing stroke corresponding with initial exposure frame number, reality corresponding with actual exposure frame number
Splicing stroke ratio initially splices that stroke is short, now needs to the initial effectively original position of light field and termination in initial gantry parameter
Position is adjusted, and obtains the original position of actually active light field and the final position of effective light field, and actually active light field rises
Beginning position and the distance between final position be actual splicing stroke, between actually active light field original position and final position
Region be actual exposure region.
In an embodiment of the present invention, it is actual in corresponding practical frame parameter when actual exposure frame number is floor (Y)
The original position Z of effective light fieldstart, actually active light field final position ZstopObtained by equation below respectively：
Zstart=Zstart0-(L0-L1)/2；
Zstop=Zstop0+(L0-L1)/2；
The height of actually active light field then with it is initial effectively light field height h0It is equal.
If 2) actual exposure frame number is floor (Y)+1, in order to avoid patient receives excessive dose of radiation, actual exposure
Region is identical with pre-exposure region, and now actual splicing stroke is identical with initial splicing stroke, therefore is not required to initial effectively light field
Original position and final position be adjusted.For the frame number for meeting the sequence image for shooting is floor (Y)+1, then need to first
The height of effective light field that begins is adjusted to obtain the height of actually active light field, and the height of actually active light field is first less than described
The height of effective light field that begins.In an embodiment of the present invention, it is corresponding actually active when actual exposure frame number is floor (Y)+1
The original position Z of the original position of light field and initial effectively light fieldstart0It is identical, the final position of actually active light field and initial
The final position Z of effective light fieldstop0Identical, the height h of actually active light field is obtained by equation below：
H=Lp+(L0-Lp)/(floor(Y)+1)。
As shown in the above, in an embodiment of the present invention, when initial exposure frame number is integer, actual exposure frame number
Equal with initial exposure frame number, practical frame parameter is identical with initial gantry parameter, i.e. actual exposure region and pre-exposure region
It is identical.When initial exposure frame number is non-integer, according to the rate of change of image mosaic stroke, the actual exposure frame number for obtaining is small
Add 1 in the max-int of initial exposure frame number or less than the max-int of initial exposure frame number.
When actual exposure frame number is the max-int less than initial exposure frame number, the initial effectively light field start bit of adjustment
Put and final position so that the actual exposure region between actually active light field original position and final position is less than initial exposure
Region.And when actual exposure frame number is less than the max-int of initial exposure frame number plus 1, actually active light field original position
Actual exposure region and final position between is equal to initial exposure region, and the height of actually active light field is less than initial effectively light
Wild height.
That is, in an embodiment of the present invention, when shooting sequence X ray image, actual exposure region is little all the time
In initial exposure region.During relative to existing shooting sequence X ray image, when initial exposure frame number is non-integer,
Actual exposure region is consistently greater than for initial exposure region, the embodiment of the present invention shoot sequence X ray image during,
Reduce the dose of radiation that patient receives.Further, since in the embodiment of the present invention, determination and the image of actual exposure frame number are spelled
The rate of change for connecing stroke is related, therefore, no matter actual exposure frame number is floor (Y) or floor (Y)+1, spliced image
It is satisfied by actual clinical demand.
Step S103 is performed, based on the actual exposure frame number and the practical frame parameter, collection is calculated per two field picture
When the corresponding detector position and bulb anglec of rotation.
In embodiments of the present invention, from step S101~S102, the actual exposure frame number of acquisition is probably initial exposure
Light frame number, it is also possible to be less than the maximum integer or the maximum integer less than the initial exposure frame number of the initial exposure frame number
Plus 1.For different actual exposure frame numbers, its corresponding practical frame parameter is also differed.Separately below to actual exposure frame
When number takes different value, the calculating of corresponding detector position and the bulb anglec of rotation is illustrated when collection is per two field picture.
In embodiments of the present invention, the focal position of bulb change in the Z-axis direction is much smaller than SID, therefore bulb
Focal position can approx be regarded as and not change in the Z-axis direction, and bulb is only around axle RHA in XZ Plane Rotations.Adopting
During collection sequence image, the height of the focus 9 of bulb 7 is not changed, and bulb 7 is existed by second support 81 around axle RHA
XZ Plane Rotations, i.e., with bulb central point 10 be rotation axis points around axle RHA in XZ Plane Rotations (referring to Fig. 2 and Fig. 3), detector
3 are done corresponding elevating movement along column in Z-direction.
(1)：Actual exposure frame number is identical with the initial exposure frame number being calculated.
From step S102, when initial exposure frame number is integer, actual exposure frame number is equal with initial exposure frame number,
Initial gantry parameter is practical frame parameter, is not required to be adjusted initial gantry parameter.
In an embodiment of the present invention, can be according to every two field picture initial bit on the detector in the sequence image of collection
Put to determine that detector is in the position of Z axis before each two field picture is obtained, namely obtain during acquisition sequence image,
The movement locus of detector.
Referring to Fig. 4, the length of the overlapping region between adjacent two field pictures is Lp.The initial position of the first two field picture is：
The upper edge of effective light field 201 corresponding with the first two field picture, height value Z1=Zstart0；The initial position of the second two field picture is：
The upper edge of effective light field 202 corresponding with the second two field picture, height value Z2=Zstart0-h0+Lp；By that analogy, n-th frame image
Initial position be effective light field corresponding with n-th frame image upper edge, height value Zn=Zstart0-(n-1)×h0+(n-1)
×Lp, wherein, n is exposure frame number.
As shown in the above, effective light field refers to that what is received on detector can form the light field model of effective image
Enclose, thus effective light field according to corresponding to the image for collecting position change in the Z-axis direction, it may be determined that detector
Change in location in the Z-axis direction.
In an embodiment of the present invention, using detector center as detector position.With reference to Fig. 4, according to every frame figure
As the upper edge height value of corresponding effective light field, it can be deduced that corresponding detector center during the first two field picture of collection
Height value ZFD1=Z1-(h0/ 2)=Zstart0-(h0/ 2), the height of corresponding detector center during the second two field picture of collection
Value ZFD2=Z2-(h0/ 2)=Zstart0-(3/2)×h0+Lp, by that analogy, corresponding detector center during collection n-th frame image
The height value Z of positionFDn=Zn-(h0/ 2)=Zstart0-((2×n-1)/2)×h0+(n-1)×Lp, wherein, n is exposure frame number.
The corresponding bulb anglec of rotation is calculated during below to collection per two field picture.In an embodiment of the present invention, ball
The pipe anglec of rotation refers to：The angle of corresponding the bulb axis of bulb and X-axis in XZ Plane Rotations during collection current frame image,
The difference of corresponding bulb angle of the axis and X-axis of bulb in XZ Plane Rotations during with collection previous frame image.Namely bulb
During from collection previous frame image to collection current frame image, the angle that bulb is turned over.
For example, corresponding bulb axis of bulb in XZ Plane Rotations is with the angle of X-axis during collection current frame image
A, corresponding the bulb axis of bulb and angle of X-axis in XZ Plane Rotations are B during collection previous frame image, then gather current
The corresponding bulb anglec of rotation is α=A-B during two field picture.Reference picture 2 and Fig. 3, the axis of bulb is with the angle of X-axis：Bulb 7
Around axle RHA in XZ Plane Rotations with the angle of X-axis.
Fig. 5 be the embodiment of the present invention in, collection n-th frame image when bulb rotation angle schematic diagram.In Fig. 5, G points are
The rotation axis points of bulb, M points and Q points are the focal position of the corresponding bulb of adjacent two field pictures, the angle α between GM and GQRHA
The angle of bulb rotation when as gathering n-th frame image.
Rotation axis points G is in the X-axis direction E points with the intersection point of detector, and bulb focus M is with detector in the X-axis direction
Intersection point be A points, bulb be irradiated to the effective light field on detector be between D points and B points, C points be bulb ray open country in
The intersection point of vertical line and detector, N points are M points and horizontal perpendicular intersection.Angle between MA and MD is α2, between MA and MB
Angle be α1, the angle between MA and MC is α3。
The distance between Q points and E points QE are source image away from SSID(Source Image Distance, SID), can be with by Fig. 5
Learn, MA=QE+NQ=QE+GM × (1-cosaRHA).In actual applications, length of the length of GM much smaller than QE, therefore can
To make GM × (1-cosaRHA, then there are MA=QE, i.e. MA=S in)=0SID。
The height value of M points is ZTCS.D points are the upper edge of the corresponding effective light field of n-th frame image, and the height value of D points is Zn
=Zstart0-(n-1)×h0+(n-1)×Lp.B points are the lower edge of the corresponding effective light field of n-th frame image, and the height value of B points is
Zn-h0, then DA=Z can be learntn-ZTCS, BA=DA-h0=Zn-ZTCS-h0。
Can be learnt from Fig. 5Wherein： Respectively willWithSubstitute into, then have：
By MA=SSID, DA=Zn-ZTCS, BA=DA-h0=Zn-ZTCS-h0Bring above formula into successively, α can be obtainedRHAFor：
αRHAWhen as collection n-th frame image, the angle of the bulb axis of bulb and X-axis in XZ Plane Rotations and is adopted
The difference of bulb angle of the axis and X-axis of bulb in XZ Plane Rotations when collecting the (n-1)th two field picture.
(2)：The actual exposure frame number for getting is less than the initial exposure frame number being calculated.
From step S102, when the actual exposure frame number for getting is floor (Y), the starting of actually active light field
Position is Zstart=Zstart0-(L0-L1)/2, the final position of actually active light field is Zstop=Zstop0+(L0-L1)/2, it is actual
The height of effective light field is h0。
With (1) similarly, still can according in the sequence image of collection per two field picture initial position on the detector,
Obtain during acquisition sequence image, the movement locus of detector.In one embodiment of the invention, the first two field picture it is initial
Position is：The upper edge of effective light field corresponding with the first two field picture, height value Z1=Zstart；The initial position of the second two field picture
For：The upper edge of effective light field corresponding with the second two field picture, height value Z2=Zstart-h0+Lp；By that analogy, n-th frame image
Initial position for the corresponding effective light field of n-th frame image upper edge, height value Zn=Zstart-(n-1)×h0+(n-1)×
Lp, n is exposure frame number.
In an embodiment of the present invention, using detector center as detector position.It is similar with (1), collection
The height value Z of corresponding detector center during the first two field pictureFD1=Zstart-(h0/ 2), correspondence during the second two field picture of collection
Detector center height value ZFD2=Zstart-(3/2)×h0+Lp, it is by that analogy, corresponding during collection n-th frame image
The height value of detector center is：ZFDn=Zstart-((2×n-1)/2)×h0+(n-1)×Lp, n is exposure frame number.
The calculating process of the height value of the detector center from (2) corresponding to every two field picture can be seen that to be compared
In (1), in (2) corresponding practical frame parameter, the original position and final position of actually active light field are no longer effective with initial
The original position of light field is identical with final position, but to the initial effectively original position of light field and after final position is adjusted
Obtain.Therefore at calculating detector center, the Z of above formula need to only be madestart=Zstart0-(L0-L1)/2, you can.
Correspondingly, the corresponding bulb anglec of rotation of collection n-th frame image is being calculated：
When, be still only need byEnter Z for Ln=Zstart-(n-1)×h0+(n-1)×
LpIn.In above formula, SSID、ZTCSImplication be referred to (1), ZnIt is the upper edge of n-th frame image corresponding effective light field
Height value.
(3)：The actual exposure frame number for getting is more than the initial exposure frame number being calculated.
Knowable to from step S102, compared to (1), not to initial effectively light field in (3) corresponding practical frame parameter
Original position and final position are adjusted, and only the height to initial effectively light field is adjusted, actually active light after adjustment
Wild height is h, therefore when detector center in (3) and the bulb anglec of rotation calculate, it is only necessary to by (1)
The height for being highly changed to actually active light field with the initial effective light field in the initial effectively parameter of the height correlation of light field is i.e.
Can.Therefore, corresponding detector position is when collection is per two field picture in (3)：
ZFDn=Zstart0-((2n-1)/2)×h+(n-1)×Lp；
The corresponding bulb anglec of rotation is when collection is per two field picture：
Wherein,H=Lp+(L0-Lp)/(floor (Y)+1), L0=
Zstart0-Zstop0。
Step S104 is performed, corresponding detector position and bulb during with the practical frame parameter, collection per two field picture
The anglec of rotation is exposed, and obtains image to be spliced.
In actual clinical application, initial gantry parameter and adjacent two can be input into according to the area in pre-exposure region
The overlapping region of two field picture, (initial gantry parameter can also be provided when X-ray shooting system is initialized by system) motion
Control unit calculates initial exposure frame number according to the information of input, according to above-mentioned mode finally obtain actual exposure frame number and
Practical frame parameter.During shooting, it is only necessary to according to motion control unit obtain practical frame parameter in, actually active light field just
Beginning position and final position, initial position in whole shooting process of manual setting ox head (including beam-defining clipper and bulb) and
Final position, presses exposure handbrake, you can with carry out sequence exposure (in sequence exposure process, the rotation of bulb and detector
Motion is by motion control unit control realization), to obtain image to be spliced.Due to the process in actual photographed sequence image
In, doctor is only needed to after the initial position and final position of manual setting ox head, is pressed exposure handbrake and be can be carried out sequence
Row exposure, therefore the workflow of sequence exposure is considerably simplify, improve operating efficiency.
In sum, initial exposure frame number is obtained according to pre-exposure region, initial exposure frame number is adjusted and obtains reality
Border exposes frame number and its corresponding practical frame parameter so that the corresponding actual exposure region of actual exposure frame number is not more than pre-exposure
The absolute value of the difference between light region, and actual exposure frame number and initial exposure frame number is less than 1.Such that it is able to avoid in reality
In clinic, when initial exposure frame number is non-integer, the integer more than initial exposure frame number is only taken as actual exposure frame number
Cause actual exposure region more than pre-exposure region, and then cause detected object to receive excessive dose of radiation, you can with effective
Reduce the dose of radiation of detected object receiving in photographic process in ground.
Additionally, in photographic process, the height due to bulb in Z-direction is fixed, it rotates in XZ planes, detection
The position of device is then as being rotated in Z-direction for bulb is adjusted correspondingly so that the matter of the sequence image that photography is obtained
Amount can meet actual clinical demand, and then also improve spliced picture quality.
The embodiment of the present invention additionally provides a kind of radioscopic image acquisition device 60, reference picture 6, including：First computing unit
601st, first acquisition unit 602, the second computing unit 603 and image acquisition unit 604, wherein：
First computing unit 601, for setting initial gantry parameter and adjacent two field pictures according to pre-exposure region
Overlapping region, calculating carries out the initial exposure frame number of image mosaic；Gantry parameter includes：The original position of effective light field, termination
Position and the height of effective light field, at least include having described in two between the original position and final position of effective light field
The height of light field is imitated, the height of effective light field is related to the openings of sizes of beam-defining clipper on vertical direction；
First acquisition unit 602, actual exposure frame number is obtained for adjusting the initial exposure frame number, and according to the reality
Border exposure frame number determines practical frame parameter so that actual exposure region is not more than the pre-exposure region, and the actual exposure
Light frame number is less than 1 with the absolute value of the difference of the initial exposure frame number；
Second computing unit 603, for according to the exposure frame number, calculating corresponding detector position when gathering per two field picture
Put and the bulb anglec of rotation；
Image acquisition unit 604, corresponding detector position during for the practical frame parameter, collection per two field picture
And the bulb anglec of rotation is exposed, image to be spliced is obtained.
The specific implementation of the radioscopic image acquisition device may be referred to the implementation of above-mentioned radioscopic image acquisition methods, this
Place repeats no more.
One of ordinary skill in the art will appreciate that realizing the whole of radioscopic image acquisition device described in above-described embodiment
Or part can be by program to instruct the hardware of correlation to complete, the program can be stored in a computer-readable storage medium
In matter, storage medium can include：ROM, RAM, disk or CD etc..
Although present disclosure is as above, the present invention is not limited to this.Any those skilled in the art, are not departing from this
In the spirit and scope of invention, can make various changes or modifications, therefore protection scope of the present invention should be with claim institute
The scope of restriction is defined.
Claims (11)
1. a kind of radioscopic image acquisition methods, it is characterised in that including：
According to the initial gantry parameter of pre-exposure region setting and the overlapping region of adjacent two field pictures, calculating carries out image mosaic
Initial exposure frame number；Gantry parameter includes：The height of the original position, final position and effective light field of effective light field, institute
Stating at least includes two height of effective light field, effective light field between the original position and final position of effective light field
Height it is related to the openings of sizes of beam-defining clipper on vertical direction；
Adjust the initial exposure frame number and obtain actual exposure frame number, when the initial exposure frame number is integer, the actual exposure
Light frame number is the initial exposure frame number；When the initial exposure frame number is non-integer, the actual exposure frame number is associated with figure
As the rate of change of splicing stroke；
Practical frame parameter is determined according to the actual exposure frame number so that actual exposure region is not more than the pre-exposure area
Domain, and the actual exposure frame number is less than 1 with the absolute value of the difference of the initial exposure frame number；
Based on the actual exposure frame number and the practical frame parameter, corresponding detector position when calculating collection per two field picture
And the bulb anglec of rotation；
Corresponding detector position and the bulb anglec of rotation are exposed during with the practical frame parameter, collection per two field picture,
Obtain image to be spliced.
2. radioscopic image acquisition methods as claimed in claim 1, it is characterised in that being calculated by equation below carries out image
The initial exposure frame number of splicing：
Y=(L0-Lp)/(h0-Lp)；
Wherein, Y is initial exposure frame number, LpIt is the overlapping region of adjacent two field pictures, h0It is the height of initial effectively light field, L0
It is initial splicing stroke；
The initial splicing stroke L0Obtained by equation below：
L0=Zstart0-Zstop0；
Wherein, Zstart0It is the original position of initial effectively light field, Zstop0It is the final position of initial effectively light field.
3. radioscopic image acquisition methods as claimed in claim 2, it is characterised in that described image splices the rate of change of stroke
Obtained by equation below：
P=(L0-L1)/L0；
Wherein, L1It is default splicing stroke, P is the rate of change of image mosaic stroke；
The default splicing stroke L1Obtained by equation below：
L1=floor (Y) × (h0-Lp)+Lp；
Wherein, function floor (x) is to take the maximum integer less than x.
4. radioscopic image acquisition methods as claimed in claim 3, it is characterised in that when the actual exposure frame number is initial
Exposure frame number, the practical frame parameter is initial gantry parameter, described based on the actual exposure frame number and the reality
Gantry parameter, corresponding detector position is carried out by equation below when calculating collection per two field picture：
ZFDn=Zstart0-((2n-1)/2)×h0+(n-1)×Lp；
Wherein, ZFDnCorresponding detector center during for collection n-th frame image, n is exposure frame number；
It is described based on the actual exposure frame number and the practical frame parameter, corresponding bulb rotation when calculating collection per two field picture
Gyration is carried out by equation below：
Wherein, αRHADuring for collection n-th frame image, the angle of the bulb axis of bulb and X-axis in XZ Plane Rotations, with collection
The difference of bulb angle of the axis and X-axis of bulb in XZ Plane Rotations during the (n-1)th two field picture；It is arc tangent letter
Number, SSIDIt is source image away from ZTCSIt is the bulb focus and the distance of ground level, ZnIt is the initial position of n-th frame image；
The initial position Z of the n-th frame imagenObtained by equation below：
Zn=Zstart0-(n-1)×h0+(n-1)×Lp。
5. radioscopic image acquisition methods as claimed in claim 1, it is characterised in that when described image splices the change of stroke
Rate is less than or equal to predetermined threshold value, and the actual exposure frame number is less than the maximum integer of the initial exposure frame number.
6. radioscopic image acquisition methods as claimed in claim 5, it is characterised in that when the actual exposure frame number be less than
The maximum integer of the initial exposure frame number, initially there is the height of actually active light field for described in corresponding practical frame parameter
Imitate the height of light field, the original position Z of actually active light fieldstartAnd final position ZstopObtained by equation below respectively：
Zstart=Zstart0-(L0-L1)/2；
Zstop=Zstop0+(L0-L1)/2。
7. radioscopic image acquisition methods as claimed in claim 6, it is characterised in that described based on the actual exposure frame number
With the practical frame parameter, corresponding detector position is carried out by equation below when calculating collection per two field picture：
ZFDn=Zstart-((2n-1)/2)×h0+(n-1)×Lp；
Wherein, ZFDnCorresponding detector center during for collection n-th frame image, n is exposure frame number；
It is described based on the actual exposure frame number and the practical frame parameter, corresponding bulb rotation when calculating collection per two field picture
Gyration is carried out by equation below：
Wherein, αRHAThe angle of the bulb axis of bulb and X-axis in XZ Plane Rotations during for collection n-th frame image, with collection the
The difference of bulb difference of the angle of the axis and X-axis of bulb in XZ Plane Rotations during n-1 two field pictures；It is arc tangent letter
Number, SSIDIt is source image away from ZTCSIt is the bulb focus and the distance of ground level, ZnIt is the initial position of n-th frame image；
The initial position Z of the n-th frame imagenObtained by equation below：
Zn=Zstart-(n-1)×h0+(n-1)×Lp。
8. radioscopic image acquisition methods as claimed in claim 1, it is characterised in that when described image splices the change of stroke
Rate is more than predetermined threshold value, and the actual exposure frame number is plus 1 less than the maximum integer of the initial exposure frame number.
9. radioscopic image acquisition methods as claimed in claim 8, it is characterised in that when the actual exposure frame number is described
The maximum integer of initial exposure frame number adds 1, and the original position of actually active light field is initially have in corresponding practical frame parameter
The original position of light field is imitated, the final position of actually active light field is the final position of initial effectively light field, actually active light field
Height by equation below obtain：
H=Lp+(L0-Lp)/(floor(Y)+1)。
10. radioscopic image acquisition methods as claimed in claim 9, it is characterised in that described based on the actual exposure frame number
With the practical frame parameter, corresponding detector position is carried out by equation below when calculating collection per two field picture：
ZFDn=Zstart0-((2n-1)/2)×h+(n-1)×Lp；
Wherein, ZFDnCorresponding detector center during for collection n-th frame image, n is exposure frame number；
It is described based on the actual exposure frame number and the practical frame parameter, corresponding bulb rotation when calculating collection per two field picture
Gyration is carried out by equation below：
Wherein, αRHAThe angle of the bulb axis of bulb and X-axis in XZ Plane Rotations during for collection n-th frame image, with collection the
The difference of bulb angle of the axis and X-axis of bulb in XZ Plane Rotations during n-1 two field pictures；It is arctan function,
SSIDIt is source image away from ZTCSIt is the bulb focus and the distance of ground level, ZnIt is the initial position of n-th frame image；
The initial position Z of the n-th frame imagenObtained by equation below：
Zn=Zstart0-(n-1)×h+(n-1)×Lp。
A kind of 11. radioscopic image acquisition device, it is characterised in that including：
First computing unit, for the overlay region according to the initial gantry parameter of pre-exposure region setting and adjacent two field pictures
Domain, calculating carries out the initial exposure frame number of image mosaic；Gantry parameter includes：The original position of effective light field, final position with
And the height of effective light field, two effective light fields are at least included between the original position and final position of effective light field
Height, the height of effective light field is related to the openings of sizes of beam-defining clipper on vertical direction；
First acquisition unit, obtains actual exposure frame number, when the initial exposure frame number for adjusting the initial exposure frame number
It is integer, the actual exposure frame number is the initial exposure frame number；When the initial exposure frame number is non-integer, the reality
Exposure frame number is associated with the rate of change of image mosaic stroke；Practical frame parameter is determined according to the actual exposure frame number so that
Actual exposure region is not more than the pre-exposure region, and the actual exposure frame number and the difference of the initial exposure frame number
Absolute value is less than 1；
Second computing unit, for based on the actual exposure frame number and the practical frame parameter, calculating collection per two field picture
When the corresponding detector position and bulb anglec of rotation；
Image acquisition unit, corresponding detector position and bulb during for the practical frame parameter, collection per two field picture
The anglec of rotation is exposed, and obtains image to be spliced.
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| US11763424B2 (en) | 2018-06-04 | 2023-09-19 | Shanghai United Imaging Healthcare Co., Ltd. | Devices, systems, and methods for image stitching |
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| CN111603187A (en) * | 2019-02-25 | 2020-09-01 | 上海西门子医疗器械有限公司 | Adaptive image quality optimization method and apparatus, storage medium, and medical device |
| CN111603187B (en) * | 2019-02-25 | 2024-02-13 | 上海西门子医疗器械有限公司 | Adaptive image quality optimization method and device, storage medium and medical equipment |
| CN110301924A (en) * | 2019-07-08 | 2019-10-08 | 东软医疗系统股份有限公司 | Handle the method, device and equipment of image |
| CN110301924B (en) * | 2019-07-08 | 2023-05-30 | 东软医疗系统股份有限公司 | Method, device and equipment for processing image |
| CN114010963A (en) * | 2021-11-08 | 2022-02-08 | 上海联影医疗科技股份有限公司 | System, method and computer-readable storage medium for dose determination |
| CN114010963B (en) * | 2021-11-08 | 2023-10-20 | 上海联影医疗科技股份有限公司 | System, method and computer readable storage medium for dose determination |
Also Published As
| Publication number | Publication date |
|---|---|
| CN106852697B (en) | 2020-12-18 |
| CN104287756A (en) | 2015-01-21 |
| CN104287756B (en) | 2017-03-08 |
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