CN106852697B - X-ray image acquisition method and device - Google Patents
X-ray image acquisition method and device Download PDFInfo
- Publication number
- CN106852697B CN106852697B CN201611267562.8A CN201611267562A CN106852697B CN 106852697 B CN106852697 B CN 106852697B CN 201611267562 A CN201611267562 A CN 201611267562A CN 106852697 B CN106852697 B CN 106852697B
- Authority
- CN
- China
- Prior art keywords
- actual
- initial
- image
- frame
- frame number
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/54—Control of apparatus or devices for radiation diagnosis
- A61B6/542—Control of apparatus or devices for radiation diagnosis involving control of exposure
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/54—Control of apparatus or devices for radiation diagnosis
- A61B6/545—Control of apparatus or devices for radiation diagnosis involving automatic set-up of acquisition parameters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/58—Testing, adjusting or calibrating apparatus or devices for radiation diagnosis
- A61B6/587—Alignment of source unit to detector unit
Abstract
An X-ray image acquisition method and device, wherein the acquisition method comprises the following steps: setting initial frame parameters and an overlapping area of two adjacent frames of images according to the pre-exposure area, and calculating the number of initial exposure frames for image splicing; adjusting the initial exposure frame number to obtain an actual exposure frame number, and determining actual frame parameters according to the actual exposure frame number, so that an actual exposure area is not larger than the pre-exposure area, and the absolute value of the difference between the actual exposure frame number and the initial exposure frame number is smaller than 1; calculating the corresponding detector position and the bulb tube rotation angle when each frame of image is collected based on the actual exposure frame number and the actual frame parameter; and exposing according to the actual frame parameters, the corresponding detector position when each frame of image is collected and the rotating angle of the bulb tube to obtain the image to be spliced. By adopting the method and the device, the object to be detected can be effectively prevented from receiving excessive radiation dose in the photographing process.
Description
The present application is a divisional application of a chinese patent application filed on 28/09/2014, having an application number of 201410508290.0 and entitled "X-ray image acquisition method and apparatus".
Technical Field
The invention relates to the technical field of image processing, in particular to an X-ray image acquisition method and device.
Background
An X-ray photography system is adopted to take a large-size and large-view-field image, such as: capturing bone images, spine images, etc. has become a widespread application.
At present, due to the physical characteristics of the X-ray imaging system, such as the area limitation of the detector, the Source Image Distance (SID) Distance limitation, etc., when imaging a large-sized portion to be imaged, it is common to perform serial imaging by dividing the large-sized portion to be imaged into single images according to the size requirement that the detector can meet, and then perform fusion, stitching, and processing on the serial images obtained by imaging through the Image workstation to obtain a large-sized Image.
However, when the above-mentioned method is used to photograph a large-sized portion to be photographed, the subject may receive an excessive radiation dose, which may cause a certain damage to the subject.
Disclosure of Invention
The problem solved by the embodiment of the invention is how to avoid the excessive radiation dose received by the detected object in the photographing process.
To solve the above problem, an embodiment of the present invention provides an X-ray image acquisition method, including:
setting initial frame parameters and an overlapping area of two adjacent frames of images according to the pre-exposure area, and calculating the number of initial exposure frames for image splicing; the rack parameters include: the beam limiting device comprises an initial position, an end position and the height of an effective light field, wherein the initial position and the end position of the effective light field at least comprise the heights of two effective light fields, and the height of the effective light field is related to the size of an opening of the beam limiting device in the vertical direction;
adjusting the initial exposure frame number to obtain an actual exposure frame number, wherein when the initial exposure frame number is an integer, the actual exposure frame number is the initial exposure frame number; when the initial exposure frame number is a non-integer, the actual exposure frame number is related to the change rate of an image splicing process;
determining actual frame parameters according to the actual exposure frame number, so that an actual exposure area is not larger than the pre-exposure area, and the absolute value of the difference between the actual exposure frame number and the initial exposure frame number is smaller than 1;
calculating the corresponding detector position and the bulb tube rotation angle when each frame of image is collected based on the actual exposure frame number and the actual frame parameter;
and exposing according to the actual frame parameters, the corresponding detector position when each frame of image is collected and the rotating angle of the bulb tube to obtain the image to be spliced.
Optionally, the initial exposure frame number for image stitching is calculated by the following formula:
Y＝(L0-Lp)/(h0-Lp)；
wherein Y is the initial exposure frame number, LpIs the overlapping area of two adjacent frame images, h0Is the height of the initial effective light field, L0An initial splicing stroke;
the initial splicing stroke L0Obtained by the following formula:
L0＝Zstart0-Zstop0；
wherein Z isstart0Is the starting position of the initial effective light field, Zstop0Is the termination position of the initial effective light field.
Optionally, the change rate of the image stitching process is obtained by the following formula:
P＝(L0-L1)/L0；
wherein L is1The image splicing process is a preset splicing process, and P is the change rate of the image splicing process;
the preset splicing stroke L1Obtained by the following formula:
L1＝floor(Y)×(h0-Lp)+Lp；
wherein the function floor (x) is the largest integer less than x.
Optionally, when the actual exposure frame number is an initial exposure frame number, the actual frame parameter is an initial frame parameter, and the calculating of the corresponding detector position when each frame of image is acquired based on the actual exposure frame number and the actual frame parameter is performed by using the following formula:
ZFDn＝Zstart0-((2n-1)/2)×h0+(n-1)×Lp；
wherein Z isFDnThe central position of a corresponding detector when the nth frame of image is collected, wherein n is the number of exposure frames;
and calculating the corresponding bulb tube rotation angle when each frame of image is acquired based on the actual exposure frame number and the actual frame parameter by the following formula:
wherein alpha isRHAThe difference between the included angle between the axis of the bulb and the X axis when the bulb rotates on the XZ plane during the collection of the nth frame image and the included angle between the axis of the bulb and the X axis when the bulb rotates on the XZ plane during the collection of the (n-1) th frame image;
as an arctangent function, SSIDIs the source image distance, ZTCSIs the distance, Z, between the focal point of the bulb and the ground planenThe initial position of the nth frame image;
initial position Z of the n-th frame imagenObtained by the following formula:
Zn＝Zstart0-(n-1)×h0+(n-1)×Lp。
optionally, when the change rate of the image stitching process is less than or equal to a preset threshold, the actual exposure frame number is a maximum integer less than the initial exposure frame number.
Optionally, when the actual exposure frame number is a maximum integer smaller than the initial exposure frame number, the height of the actual effective field in the corresponding actual frame parameter is the height of the initial effective field, and the starting position Z of the actual effective fieldstartAnd a termination position ZstopAre respectively obtained by the following formulas:
Zstop＝Zstop0+(L0-L1)/2。
optionally, calculating, based on the actual exposure frame number and the actual frame parameter, a position of the detector corresponding to each frame of the acquired image according to the following formula:
ZFDn＝Zstart-((2n-1)/2)×h0+(n-1)×Lp；
wherein Z isFDnThe central position of a corresponding detector when the nth frame of image is collected, wherein n is the number of exposure frames;
and calculating the corresponding bulb tube rotation angle when each frame of image is acquired based on the actual exposure frame number and the actual frame parameter by the following formula:
wherein alpha isRHAThe difference between the included angle between the axis of the bulb and the X axis when the bulb rotates on the XZ plane during the collection of the nth frame image and the included angle between the axis of the bulb and the X axis when the bulb rotates on the XZ plane during the collection of the (n-1) th frame image;
as an arctangent function, SSIDIs the source image distance, ZTCSIs the distance, Z, between the focal point of the bulb and the ground planenThe initial position of the nth frame image;
initial position Z of the n-th frame imagenObtained by the following formula:
Zn＝Zstart-(n-1)×h0+(n-1)×Lp。
optionally, when the change rate of the image stitching process is greater than a preset threshold, the actual exposure frame number is the maximum integer smaller than the initial exposure frame number plus 1.
Optionally, when the actual exposure frame number is the maximum integer of the initial exposure frame number plus 1, the start position of the actual effective field in the corresponding actual frame parameter is the start position of the initial effective field, the end position of the actual effective field is the end position of the initial effective field, and the height of the actual effective field is obtained through the following formula:
h＝Lp+(L0-Lp)/(floor(Y)+1)。
optionally, calculating, based on the actual exposure frame number and the actual frame parameter, a position of the detector corresponding to each frame of the acquired image according to the following formula:
ZFDn＝Zstart0-((2n-1)/2)×h+(n-1)×Lp；
wherein Z isFDnThe central position of a corresponding detector when the nth frame of image is collected, wherein n is the number of exposure frames;
and calculating the corresponding bulb tube rotation angle when each frame of image is acquired based on the actual exposure frame number and the actual frame parameter by the following formula:
wherein alpha isRHAThe difference between the included angle between the axis of the bulb and the X axis when the bulb rotates on the XZ plane during the collection of the nth frame image and the included angle between the axis of the bulb and the X axis when the bulb rotates on the XZ plane during the collection of the (n-1) th frame image;
as an arctangent function, SSIDIs the source image distance, ZTCSIs the distance, Z, between the focal point of the bulb and the ground planenThe initial position of the nth frame image;
initial position Z of the n-th frame imagenObtained by the following formula:
Zn＝Zstart0-(n-1)×h+(n-1)×Lp。
to solve the above problem, an embodiment of the present invention further provides an X-ray image acquisition apparatus, including:
the first calculation unit is used for setting initial frame parameters and an overlapping area of two adjacent frames of images according to the pre-exposure area and calculating the number of initial exposure frames for image splicing; the rack parameters include: the beam limiting device comprises an initial position, an end position and the height of an effective light field, wherein the initial position and the end position of the effective light field at least comprise the heights of two effective light fields, and the height of the effective light field is related to the size of an opening of the beam limiting device in the vertical direction;
a first obtaining unit, configured to adjust the initial exposure frame number to obtain an actual exposure frame number, where when the initial exposure frame number is an integer, the actual exposure frame number is the initial exposure frame number; when the initial exposure frame number is a non-integer, the actual exposure frame number is related to the change rate of an image splicing process; determining actual frame parameters according to the actual exposure frame number, so that an actual exposure area is not larger than the pre-exposure area, and the absolute value of the difference between the actual exposure frame number and the initial exposure frame number is smaller than 1;
the second calculation unit is used for calculating the corresponding detector position and the bulb tube rotation angle when each frame of image is collected based on the actual exposure frame number and the actual frame parameter;
and the image acquisition unit is used for carrying out exposure according to the actual frame parameters, the corresponding detector position when each frame of image is acquired and the rotating angle of the bulb tube, and acquiring the images to be spliced.
Compared with the prior art, the technical scheme of the embodiment of the invention has the following advantages:
and acquiring an initial exposure frame number according to the pre-exposure area, adjusting the initial exposure frame number to obtain an actual exposure frame number and an actual frame parameter corresponding to the actual exposure frame number, so that an actual exposure area corresponding to the actual exposure frame number is not larger than the pre-exposure area, and the absolute value of the difference between the actual exposure frame number and the initial exposure frame number is smaller than 1. Therefore, in actual clinic, when the initial exposure frame number is a non-integer, only the integer larger than the initial exposure frame number is taken as the actual exposure frame number to cause the actual exposure area to be larger than the pre-exposure area, and further cause the detected object to receive excessive radiation dose, so that the radiation dose received by the detected object in the shooting process can be effectively reduced. The actual exposure frame number is related to the change rate of the image splicing process, and the final actual exposure frame number and the corresponding actual frame parameter are determined according to the relation between the change rate of the image splicing process and the preset threshold value, so that the image meeting the actual clinical requirement can be obtained.
In addition, in the shooting process, the height of the bulb tube in the Z-axis direction is fixed, the bulb tube only rotates in an XZ plane, and the position of the detector is correspondingly adjusted in the Z-axis direction along with the rotation of the bulb tube, so that the quality of a sequence image obtained by shooting can meet the actual clinical requirement, and the quality of the spliced image is further improved.
Drawings
FIG. 1 is a flow chart of an X-ray image acquisition method of an embodiment of the present invention;
FIG. 2 is a schematic view of an radiography system at a first time instant;
FIG. 3 is a schematic view of the radiography system at a second time instant;
FIG. 4 is a diagram illustrating an exemplary method for determining an initial exposure frame number according to an embodiment of the present invention;
FIG. 5 is a schematic diagram illustrating the rotation angle of the bulb before the nth frame of image is captured according to an embodiment of the present invention;
fig. 6 is a schematic structural diagram of an X-ray image acquisition apparatus according to an embodiment of the present invention.
Detailed Description
As described in the background, the prior art may result in an excessive radiation dose to the subject when obtaining a large-scale image. The inventor finds that, in the process of taking a large-size image, after calculating the initial exposure frame number of image stitching according to the pre-exposure area, if the initial exposure frame number is not an integer, a doctor usually takes an integer larger than the initial exposure frame number as the exposure frame number in the actual shooting process, so that the actual exposure area is larger than the pre-exposure area, and the subject receives excessive radiation dose, which causes a certain damage to the subject.
The inventor considers that the initial exposure frame number obtained by calculation is correspondingly adjusted to obtain the actual exposure frame number, so that the actual exposure area is not larger than the pre-exposure area, and the radiation dose received by the detected object in the shooting process can be reduced. Further, the initial exposure frame number is adjusted through the change rate of the image splicing process to obtain the actual exposure frame number, and the actual frame parameter corresponding to the actual exposure frame number is obtained to obtain the image meeting the actual clinical requirement.
As shown in fig. 1, an X-ray image acquisition method of an embodiment of the present invention includes:
step S101: setting initial frame parameters and an overlapping area of two adjacent frames of images according to the pre-exposure area, and calculating the number of initial exposure frames for image splicing;
step S102: adjusting the initial exposure frame number to obtain an actual exposure frame number, and determining actual frame parameters according to the actual exposure frame number, so that an actual exposure area is not larger than the pre-exposure area, and the absolute value of the difference between the actual exposure frame number and the initial exposure frame number is smaller than 1;
step S103: calculating the corresponding detector position and the bulb tube rotation angle when each frame of image is collected based on the actual exposure frame number and the actual frame parameter;
step S104: and exposing according to the actual frame parameters, the corresponding detector position when each frame of image is collected and the rotating angle of the bulb tube to obtain the image to be spliced.
In order to make the aforementioned objects, features and advantages of the embodiments of the present invention comprehensible, specific embodiments accompanied with figures are described in detail below.
Before describing the X-ray image acquisition method in detail in the embodiment of the present invention, the configuration of the X-ray imaging system employed in the embodiment of the present invention will be briefly described.
Referring to fig. 2 and 3, fig. 2 is a schematic view of an radiography system at a first time, and fig. 3 is a schematic view of the radiography system at a second time.
In fig. 2 and 3, the radiography system mainly includes: a beam 1, a bed 2, a detector 3, a column 4, a moving guide 5, a vertically telescopic suspension arm 6, and a bulb 7 (XY plane of XYZ three-dimensional coordinate system in fig. 2 and 3 is parallel to a ground plane o1), wherein: the column 4 is generally fixed on the floor of the machine room (the floor is the ground plane o1), on which the detector 3 is mounted, and the bulb 7 is provided with the beam limiter 11 for controlling the emitted light.
The detector 3 can do up-and-down lifting motion along the upright post 4, and the bulb tube 7 is connected with the suspension arm 6 through the bulb tube bracket 8; the bulb support 8 can rotate the bulb 7 in the XY plane and/or the XZ plane, respectively, and also perform vertical lifting movement together with the suspension arm 6 which can be extended and retracted vertically. The bulb holder 8 mainly includes a first holder 80 and a second holder 81 which are perpendicular to each other, and in fig. 2, the central axis of the suspension arm 6 is defined as an axis RVA and the axis RVA is parallel to the Z-axis, and the central axis of the second holder 81 is defined as an axis RHA and the axis RHA is parallel to the Y-axis. The first support 80 can drive the integral bulb support 8 and the bulb 7 to rotate about the axis RVA in the XY plane, and the second support 81 can drive the bulb 7 to rotate about the axis RHA in the XZ plane.
And S101, setting initial frame parameters and an overlapping area of two adjacent frames of images according to the pre-exposure area, and calculating the number of initial exposure frames for image splicing.
In a specific implementation, the rack parameters may include a start position, an end position, and a height of the effective light field, at least two heights of the effective light field may be included between the start position and the end position of the effective light field, and the height of the effective light field is related to the size of the opening of the beam limiter in the vertical direction. In an embodiment of the present invention, the height of the effective light field is equal to the product of the opening size of the beam limiter in the vertical direction and a constant value k, which can be set according to actual clinical requirements.
In an embodiment of the present invention, the effective light field refers to a light field range received by the detector, which can form an effective image. The starting position of the effective light field refers to the upper edge of the effective light field corresponding to the first frame image when the first frame image is shot; the termination position of the effective light field refers to the lower edge of the effective light field corresponding to the last frame image when the last frame image is shot.
In the embodiment of the invention, the pre-exposure area can be determined according to the part to be shot, and then the initial frame parameters are set, namely the frame parameters are initialized. The initial gantry parameters include: the starting position of the initial effective light field, the ending position of the initial effective light field and the height of the initial effective light field. In practical application, the parameters of the gantry may be initialized according to clinical requirements, for example, a doctor may determine a pre-exposure region according to a part to be photographed, determine a start position and an end position of an initial effective light field based on the pre-exposure region, and determine the height of the initial effective light field according to clinical requirements.
After the initial position and the end position of the initial effective light field and the height of the initial effective light field are set, the initial splicing stroke of the images to be spliced can be determined according to the initial position and the end position of the initial effective light field. And calculating the initial exposure frame number according to the initial splicing stroke, the height of the initial effective light field and the overlapping area of two adjacent frames of images in the images to be spliced.
Fig. 4 is a diagram illustrating determination of the initial exposure frame number in the embodiment of the present invention. In fig. 4, a dashed frame 201 indicates the position of the effective light field corresponding to the first frame image, and a dashed frame 20n indicates the position of the effective light field corresponding to the last frame image. The upper edge of the dashed box 201 indicates the start position of the initial effective light field, and the lower edge of the dashed box 20n indicates the end position of the initial effective light field. The solid line frame 202 indicates the position of the effective light field corresponding to the second frame image, and an overlap region having a length L exists between the solid line frame 202 and the dashed line frame 201p. The heights of the dashed boxes 201, 20n and the solid box 202 are the height h of the initial effective light field0And line 204 represents the ground plane.
As can be seen from FIG. 4, the height of the initial position of the initial effective light field relative to the ground plane is Zstart0The height value of the termination position of the initial effective light field relative to the ground plane is Zstop0According to the distance between the initial position and the end position of the initial effective light field, the initial splicing travel L of the images to be spliced can be calculated0Comprises the following steps:
L0＝Zstart0-Zstop0。
according to the initial splicing stroke L0And the length L of the overlapping area between two adjacent frame imagespCalculating the initial exposure frame number Y as:
Y＝(L0-Lp)/(h0-Lp)。
and S102 is executed, the initial exposure frame number is adjusted to obtain an actual exposure frame number, and an actual frame parameter is determined according to the actual exposure frame number, so that an actual exposure area is not larger than the pre-exposure area, and the absolute value of the difference between the actual exposure frame number and the initial exposure frame number is smaller than 1.
In this embodiment of the present invention, the initial exposure frame number calculated in step S101 may be an integer value or a non-integer value. In practical applications, the number of frames that are required to be exposed finally should be an integer value. When the initial exposure frame number is an integer value, the initial exposure frame number may not be adjusted, and the actual exposure frame number is the initial exposure frame number. When the initial exposure frame number is a non-integer value, the initial exposure frame number needs to be adjusted according to actual clinical requirements to obtain an actual exposure frame number corresponding to the integer value. For example, an integer portion of the initial exposure frame number may be taken as the actual exposure frame number. As another example, the actual exposure frame number may be taken as the integer portion of the initial exposure frame number plus 1.
In an embodiment of the present invention, when the initial exposure frame number is a non-integer, the obtaining of the actual exposure frame number is associated with the change rate of the image stitching process, and the change rate of the image stitching process is associated with the initial stitching process L0And a preset splicing stroke L1Specifically, the change rate of the image stitching process is calculated by the following formula:
P＝(L0-L1)/L0；
wherein P is the change rate of the image splicing process, L0For an initial splicing stroke, L1For the preset splicing stroke, the preset splicing stroke is as follows:
L1＝floor(Y)×(h0-Lp)+Lp；
the meaning of the function floor (x) is: taking the largest integer less than x.
And after the change rate of the image splicing process is obtained according to the formula, comparing the change rate of the image splicing process with a preset threshold value, and determining the actual exposure frame number according to the comparison result.
In an embodiment of the invention, when the change rate of the image splicing process is less than or equal to a preset threshold, it indicates that the length of the exposure frame is not enough to have little influence on the finally spliced image, and the decimal part of the initial exposure frame number is discarded, i.e. floor (Y) is used as the actual exposure frame number, and the finally obtained spliced image also meets the actual clinical requirement; and when the change rate of the image splicing process is larger than a preset threshold, the length of the image splicing process is not enough to expose one frame, so that the influence on the finally spliced image is large, and the decimal part of the initial exposure frame number cannot be discarded, namely, floor (Y) +1 is used as the actual exposure frame number.
In the embodiment of the present invention, the range of the preset threshold is [ 3%, 7% ]. Specifically, the preset threshold may be: 5%, in other embodiments, the preset threshold may also be: 6% or 7%. The doctor can set the preset threshold value correspondingly according to the actual clinical requirement.
In the embodiment of the invention, when the initial exposure frame number is an integer, the actual exposure frame number is the same as the initial exposure frame number, and at the moment, the initial frame parameter does not need to be adjusted, namely, the initial frame parameter is used as the actual frame parameter. When the initial exposure frame number is a non-integer, the initial gantry parameters need to be adjusted to determine the actual gantry parameters, so as to obtain an image meeting the actual clinical requirements and reduce the radiation dose received by the patient.
As described above, since the actual exposure frame number may be floor (Y) or floor (Y) +1, the values of the corresponding actual frame parameters will be described below when the actual exposure frame number takes different values.
1) If the actual exposure frame number is floor (Y), the actual exposure frame number is smaller than the initial exposure frame number relative to the initial exposure frame number, and the corresponding actual splicing travel is
L1＝floor(Y)×(h0-Lp)+Lp。
Therefore, relative to the initial splicing stroke corresponding to the initial exposure frame number, the actual splicing stroke corresponding to the actual exposure frame number is shorter than the initial splicing stroke, at this time, the initial position and the end position of the initial effective light field in the initial frame parameters need to be adjusted to obtain the initial position and the end position of the actual effective light field, the distance between the initial position and the end position of the actual effective light field is the actual splicing stroke, and the region between the initial position and the end position of the actual effective light field is the actual exposure region.
In an embodiment of the present invention, when the actual frame number of exposure is floor (Y), the initial position Z of the actual effective field in the corresponding actual frame parameterstartThe end position Z of the actual effective light fieldstopAre respectively obtained by the following formulas:
Zstart＝Zstart0-(L0-L1)/2；
Zstop＝Zstop0+(L0-L1)/2；
the height h of the actual effective light field is equal to the height h of the initial effective light field0Are equal.
2) If the actual exposure frame number is floor (Y) +1, in order to avoid the patient receiving excessive radiation dose, the actual exposure area is the same as the pre-exposure area, and the actual splicing stroke is the same as the initial splicing stroke, so that the initial position and the end position of the initial effective light field do not need to be adjusted. In order to meet the requirement that the frame number of the shot sequence images is floor (Y) +1, the height of the initial effective light field needs to be adjusted to obtain the height of the actual effective light field, and the height of the actual effective light field is smaller than the height of the initial effective light field. In an embodiment of the present invention, when the actual exposure frame number is floor (Y) +1, the corresponding start position of the actual effective light field and the start position Z of the initial effective light fieldstart0Similarly, the end position of the actual effective light field and the end position Z of the initial effective light fieldstop0Similarly, the height h of the actual effective light field is obtained by the following formula:
h＝Lp+(L0-Lp)/(floor(Y)+1)。
as can be seen from the above, in an embodiment of the present invention, when the initial exposure frame number is an integer, the actual exposure frame number is equal to the initial exposure frame number, and the actual frame parameter is the same as the initial frame parameter, that is, the actual exposure area is the same as the pre-exposure area. And when the initial exposure frame number is a non-integer, according to the change rate of the image splicing process, obtaining the actual exposure frame number which is the maximum integral value smaller than the initial exposure frame number or the maximum integral value smaller than the initial exposure frame number plus 1.
And when the actual exposure frame number is the maximum integral value smaller than the initial exposure frame number, adjusting the initial effective light field starting position and the ending position to ensure that the actual exposure area between the initial effective light field starting position and the ending position is smaller than the initial exposure area. And when the actual exposure frame number is the maximum integral value less than the initial exposure frame number plus 1, the actual exposure area between the initial position and the end position of the actual effective light field is equal to the initial exposure area, and the height of the actual effective light field is less than the height of the initial effective light field.
That is, in one embodiment of the present invention, the actual exposure area is always no larger than the initial exposure area when the sequential X-ray images are taken. Compared with the prior art that the actual exposure area is always larger than the initial exposure area when the initial exposure frame number is a non-integer in the process of shooting the sequence X-ray images, the embodiment of the invention reduces the radiation dosage received by a patient in the process of shooting the sequence X-ray images. In addition, since the determination of the actual exposure frame number is related to the change rate of the image stitching process in the embodiment of the invention, the stitched image meets the actual clinical requirement no matter whether the actual exposure frame number is floor (Y) or floor (Y) + 1.
And S103, calculating the corresponding detector position and the bulb tube rotation angle when each frame of image is acquired based on the actual exposure frame number and the actual frame parameter.
In the embodiment of the present invention, as can be seen from steps S101 to S102, the obtained actual exposure frame number may be the initial exposure frame number, or may be the maximum integer smaller than the initial exposure frame number or the maximum integer smaller than the initial exposure frame number plus 1. And aiming at different actual exposure frame numbers, the corresponding actual frame parameters are different. The calculation of the detector position and the bulb rotation angle corresponding to each frame of image collected when the actual exposure frame number takes different values will be described below.
In the embodiment of the present invention, the focal position of the bulb changes much less in the Z-axis direction than SID, so the focal position of the bulb can be approximately regarded as unchanged in the Z-axis direction, and the bulb rotates only about the axis RHA in the XZ plane. That is, in the process of acquiring the sequence image, the height of the focal point 9 of the bulb 7 is not changed, the bulb 7 rotates on the XZ plane around the shaft RHA through the second support 81, that is, the bulb central point 10 is taken as a rotation shaft point and rotates on the XZ plane around the shaft RHA (see fig. 2 and 3), and the detector 3 performs corresponding lifting motion along the column in the Z-axis direction.
(1): the actual exposure frame number is the same as the calculated initial exposure frame number.
As can be seen from step S102, when the initial frame exposure number is an integer, the actual frame exposure number is equal to the initial frame exposure number, and the initial frame parameter is the actual frame parameter, and the initial frame parameter does not need to be adjusted.
In an embodiment of the present invention, the position of the detector in the Z axis before obtaining each frame of image can be determined according to the initial position of each frame of image on the detector in the acquired sequence images, that is, the motion trajectory of the detector in the process of acquiring the sequence images is obtained.
Referring to fig. 4, the length of the overlapping region between two adjacent frame images is Lp. The initial position of the first frame image is: the upper edge of the effective field 201 corresponding to the first frame image, the height value Z1＝Zstart0(ii) a The initial position of the second frame image is: the upper edge of the effective field 202 corresponding to the second frame image, the height value Z2＝Zstart0-h0+Lp(ii) a By analogy, the initial position of the nth frame image is the upper edge of the effective light field corresponding to the nth frame image, and the height value Zn＝Zstart0-(n-1)×h0+(n-1)×LpWherein n is the number of exposure frames.
As can be seen from the above, the effective light field refers to a light field range received by the detector and capable of forming an effective image, and therefore, according to the change of the position of the effective light field corresponding to the acquired image in the Z-axis direction, the change of the position of the detector in the Z-axis direction can be determined.
In an embodiment of the present invention, the center position of the detector is used as the detector position. With reference to fig. 4, according to the height value of the upper edge of the effective light field corresponding to each frame of image, the height value Z of the center position of the detector corresponding to the first frame of image can be obtainedFD1＝Z1-(h0/2)＝Zstart0-(h0And/2) acquiring a height value Z of the center position of the corresponding detector when the second frame image is acquiredFD2＝Z2-(h0/2)＝Zstart0-(3/2)×h0+LpAnd so on, the height value Z of the corresponding detector center position is obtained when the nth frame image is acquiredFDn＝Zn-(h0/2)＝Zstart0-((2×n-1)/2)×h0+(n-1)×LpWherein n is the number of exposure frames.
And calculating the corresponding rotating angle of the bulb tube when each frame of image is acquired. In an embodiment of the present invention, the rotation angle of the bulb is: the difference between the included angle between the axis of the bulb and the X axis when the corresponding bulb rotates on the XZ plane when the current frame image is collected and the included angle between the axis of the bulb and the X axis when the corresponding bulb rotates on the XZ plane when the previous frame image is collected. That is, the angle the bulb tube rotates from the acquisition of the previous frame image to the acquisition of the current frame image.
For example, when the tube corresponding to the current frame image is acquired and the tube rotates on the XZ plane, the angle between the axis of the tube and the X axis is a, when the tube corresponding to the previous frame image is acquired and the tube rotates on the XZ plane, the angle between the axis of the tube and the X axis is B, and when the current frame image is acquired, the rotation angle of the tube corresponding to the current frame image is α — B. Referring to fig. 2 and 3, the axis of the bulb and the X axis form an angle: the bulb 7 makes an angle with the X-axis when rotated about the axis RHA in the XZ plane.
FIG. 5 is a schematic diagram illustrating an angle of rotation of the bulb when the nth frame of image is acquired according to the embodiment of the present invention. In FIG. 5, point G is the rotation axis point of the bulb, points M and Q are the focal positions of the bulb corresponding to two adjacent frames of images, and the included angle α between GM and GQRHANamely the angle of the bulb tube rotation when the nth frame image is collected.
The intersection point of the rotating shaft point G and the detector in the X-axis direction is a point E, the intersection point of the bulb tube focus M and the detector in the X-axis direction is a point A, the effective light field irradiated on the detector by the bulb tube is between a point D and a point B, the point C is the intersection point of the perpendicular bisector of the bulb tube ray field and the detector, and the point N is the vertical intersection point of the point M and the horizontal line. The included angle between MA and MD is alpha2The angle between MA and MB is alpha1The angle between MA and MC is alpha3。
The distance QE between the point Q and the point E is the source image distance SSID(Source Image Distance, SID), as can be seen from FIG. 5, MA QE + NQ QE + GM x (1-cosa)RHA). In practical applications, the length of GM is much smaller than that of QE, so that GM x (1-cosa) can be usedRHA) When MA is 0, MA is QE, i.e., MA is SSID。
The height value of M point is ZTCS. D point is the upper edge of the effective light field corresponding to the nth frame image, and the height value of the D point is Zn＝Zstart0-(n-1)×h0+(n-1)×Lp. The point B is the lower edge of the effective light field corresponding to the nth frame image, and the height value of the point B is Zn-h0Then, DA ═ Z can be foundn-ZTCS，BA＝DA-h0＝Zn-ZTCS-h0。
From FIG. 5, it can be seen that
Wherein:
respectively to be provided with
And
substituting, then there are:
converting MA to SSID，DA＝Zn-ZTCS，BA＝DA-h0＝Zn-ZTCS-h0By bringing into the above formula in sequence, alpha can be obtainedRHAComprises the following steps:
αRHAnamely, the difference between the included angle between the axis of the bulb and the X axis when the bulb rotates on the XZ plane for acquiring the nth frame image and the included angle between the axis of the bulb and the X axis when the bulb rotates on the XZ plane for acquiring the (n-1) th frame image.
(2): and the obtained actual exposure frame number is less than the calculated initial exposure frame number.
From step S102, when the actual exposure frame number obtained is floor (Y), the initial position of the actual effective light field is Zstart＝Zstart0-(L0-L1) /2, the termination position of the actual effective light field is Zstop＝Zstop0+(L0-L1) /2, the height of the actual effective light field is h0。
Similarly to (1), the motion track of the detector in the process of acquiring the sequence images can still be obtained according to the initial position of each frame of image in the acquired sequence images on the detector. In an embodiment of the present invention, the initial position of the first frame image is: the upper edge and height value Z of the effective light field corresponding to the first frame image1＝Zstart(ii) a The initial position of the second frame image is: the upper edge and height value Z of the effective light field corresponding to the second frame image2＝Zstart-h0+Lp(ii) a By analogy, the initial position of the nth frame image is the upper edge of the effective light field corresponding to the nth frame image, and the height value Zn＝Zstart-(n-1)×h0+(n-1)×LpAnd n is the number of exposure frames.
In one embodiment of the invention, the center of the detector is usedThe position serves as a detector position. Similar to (1), the height value Z of the corresponding detector center position at the time of acquiring the first frame imageFD1＝Zstart-(h0And/2) acquiring a height value Z of the center position of the corresponding detector when the second frame image is acquiredFD2＝Zstart-(3/2)×h0+LpAnd by analogy, the height value of the corresponding detector center position when the nth frame image is acquired is as follows: zFDn＝Zstart-((2×n-1)/2)×h0+(n-1)×LpAnd n is the number of exposure frames.
As can be seen from the calculation process of the height value of the detector center position corresponding to each frame of image in (2), compared with the actual frame parameters corresponding to (1) and (2), the start position and the end position of the actual effective light field are no longer the same as those of the initial effective light field, but are obtained after the start position and the end position of the initial effective light field are adjusted. Therefore, when the central position of the detector is calculated, only the Z of the formula is requiredstart＝Zstart0-(L0-L1) And/2, namely, obtaining the product.
Correspondingly, when the bulb rotation angle corresponding to the collected nth frame image is calculated:
then, only need to be
Substituted by L into Zn＝Zstart-(n-1)×h0+(n-1)×LpAnd (4) performing neutralization. In the above formula, SSID、ZTCSCan be referred to (1), ZnThe height value of the upper edge of the effective light field corresponding to the nth frame image is obtained.
(3): and the obtained actual exposure frame number is greater than the calculated initial exposure frame number.
As can be seen from step S102, compared with (1) and (3), the initial position and the end position of the initial effective field are not adjusted in the actual frame parameters corresponding to (1) and (3), only the height of the initial effective field is adjusted, and the height of the actual effective field after adjustment is h, so that when the center position of the detector in (3) and the rotation angle of the bulb tube are calculated, only the height of the initial effective field in the parameters related to the height of the initial effective field in (1) needs to be changed to the height of the actual effective field. Therefore, the corresponding detector positions when each frame of image is acquired in (3) are as follows:
ZFDn＝Zstart0-((2n-1)/2)×h+(n-1)×Lp；
the corresponding rotating angle of the bulb tube when each frame of image is collected is as follows:
wherein the content of the first and second substances,
h＝Lp+(L0-Lp)/(floor(Y)+1)，L0＝Zstart0-Zstop0。
and S104, exposing according to the actual frame parameters, the corresponding detector position when each frame of image is collected and the rotating angle of the bulb tube, and obtaining the images to be spliced.
In practical clinical application, initial gantry parameters and an overlapping region of two adjacent frames of images can be input according to the area of a pre-exposure region, (the initial gantry parameters can also be provided by the system when the X-ray photography system is initialized) the motion control unit calculates the initial exposure frame number according to the input information, and finally obtains the actual exposure frame number and the actual gantry parameters according to the mode. During shooting, sequence exposure can be carried out only by acquiring the initial position and the end position of an actual effective light field in actual rack parameters according to a motion control unit, manually setting the initial position and the end position of a cow head (comprising a beam limiter and a bulb tube) in the whole shooting process and pressing an exposure hand brake (in the sequence exposure process, the rotation of the bulb tube and the motion of a detector are controlled and realized by the motion control unit) so as to acquire images to be spliced. In the process of actually shooting the sequence images, a doctor can perform sequence exposure only by pressing the exposure hand brake after manually setting the initial position and the final position of the ox head, so that the workflow of the sequence exposure is simplified to a great extent, and the working efficiency is improved.
In summary, the initial exposure frame number is obtained according to the pre-exposure region, and the initial exposure frame number is adjusted to obtain the actual exposure frame number and the actual frame parameter corresponding to the actual exposure frame number, so that the actual exposure area corresponding to the actual exposure frame number is not greater than the pre-exposure region, and the absolute value of the difference between the actual exposure frame number and the initial exposure frame number is less than 1. Therefore, in actual clinic, when the initial exposure frame number is a non-integer, only the integer larger than the initial exposure frame number is taken as the actual exposure frame number to cause the actual exposure area to be larger than the pre-exposure area, and further cause the detected object to receive excessive radiation dose, so that the radiation dose received by the detected object in the shooting process can be effectively reduced.
In addition, in the shooting process, the height of the bulb tube in the Z-axis direction is fixed, the bulb tube only rotates in an XZ plane, and the position of the detector is correspondingly adjusted in the Z-axis direction along with the rotation of the bulb tube, so that the quality of a sequence image obtained by shooting can meet the actual clinical requirement, and the quality of the spliced image is further improved.
An embodiment of the present invention further provides an X-ray image obtaining apparatus 60, referring to fig. 6, including: a first calculation unit 601, a first acquisition unit 602, a second calculation unit 603, and an image acquisition unit 604, wherein:
a first calculating unit 601, configured to set an initial frame parameter and an overlapping region of two adjacent frames of images according to a pre-exposure region, and calculate an initial exposure frame number for image stitching; the rack parameters include: the beam limiting device comprises an initial position, an end position and the height of an effective light field, wherein the initial position and the end position of the effective light field at least comprise the heights of two effective light fields, and the height of the effective light field is related to the size of an opening of the beam limiting device in the vertical direction;
a first obtaining unit 602, configured to adjust the initial exposure frame number to obtain an actual exposure frame number, and determine an actual frame parameter according to the actual exposure frame number, so that an actual exposure area is not larger than the pre-exposure area, and an absolute value of a difference between the actual exposure frame number and the initial exposure frame number is smaller than 1;
a second calculating unit 603, configured to calculate, according to the exposure frame number, a position of the detector and a rotation angle of the bulb tube corresponding to each frame of image acquired;
and an image obtaining unit 604, configured to perform exposure according to the actual frame parameters, the position of the detector corresponding to each frame of image collected, and the rotation angle of the bulb, so as to obtain an image to be stitched.
For the specific implementation of the X-ray image obtaining apparatus, reference may be made to the implementation of the X-ray image obtaining method, which is not described herein again.
It will be understood by those skilled in the art that all or part of the above-described X-ray image acquisition apparatus may be implemented by a program to instruct associated hardware, and the program may be stored in a computer-readable storage medium, and the storage medium may include: ROM, RAM, magnetic or optical disks, and the like.
Although the present invention is disclosed above, the present invention is not limited thereto. Various changes and modifications may be effected therein by one skilled in the art without departing from the spirit and scope of the invention as defined in the appended claims.
Claims (9)
1. An X-ray image acquisition method characterized by comprising:
setting initial frame parameters and an overlapping area of two adjacent frames of images according to the pre-exposure area, and calculating the number of initial exposure frames for image splicing; the rack parameters include: the beam limiting device comprises an initial position, an end position and the height of an effective light field, wherein the initial position and the end position of the effective light field at least comprise the heights of two effective light fields, and the height of the effective light field is related to the size of an opening of the beam limiting device in the vertical direction;
adjusting the initial exposure frame number to obtain an actual exposure frame number, wherein when the initial exposure frame number is an integer, the actual exposure frame number is the initial exposure frame number; when the initial exposure frame number is a non-integer, the actual exposure frame number is related to the change rate of an image splicing process;
determining actual frame parameters according to the actual exposure frame number, so that an actual exposure area is not larger than the pre-exposure area, and the absolute value of the difference between the actual exposure frame number and the initial exposure frame number is smaller than 1;
calculating the corresponding detector position and the bulb tube rotation angle when each frame of image is collected based on the actual exposure frame number and the actual frame parameter;
exposing according to the actual frame parameters, the corresponding detector position when each frame of image is collected and the rotating angle of the bulb tube to obtain images to be spliced;
wherein, the change rate of the image splicing stroke is obtained by the following formula:
P＝(L0-L1)/L0；
wherein L is0For an initial splicing stroke, L1And P is the change rate of the image splicing stroke.
2. The X-ray image acquisition method as set forth in claim 1, wherein the number of initial exposure frames for image stitching is calculated by the following formula:
Y＝(L0-Lp)/(h0-Lp)；
wherein Y is the initial exposure frame number, LpIs the overlapping area of two adjacent frame images, h0Is the height of the initial effective light field;
the initial splicing stroke L0Obtained by the following formula:
L0＝Zstart0-Zstop0；
wherein Z isstart0Is the starting position of the initial effective light field, Zstop0Is the termination position of the initial effective light field;
the preset splicing stroke L1By the followingObtaining the formula:
L1＝floor(Y)×(h0-Lp)+Lp；
wherein, the function floor (x) is the maximum integer less than x;
when the actual exposure frame number is an initial exposure frame number, the actual frame parameter is an initial frame parameter, and the calculation of the corresponding detector position when each frame of image is acquired is performed through the following formula based on the actual exposure frame number and the actual frame parameter:
ZFDn＝Zstart0-((2n-1)/2)×h0+(n-1)×Lp；
wherein Z isFDnThe central position of a corresponding detector when the nth frame of image is collected, wherein n is the number of exposure frames;
and calculating the corresponding bulb tube rotation angle when each frame of image is acquired based on the actual exposure frame number and the actual frame parameter by the following formula:
wherein alpha isRHAThe difference between the included angle between the axis of the bulb and the X axis when the bulb rotates on the XZ plane during the collection of the nth frame image and the included angle between the axis of the bulb and the X axis when the bulb rotates on the XZ plane during the collection of the (n-1) th frame image; arctan () is an arctangent function, SSIDIs the source image distance, ZTCSIs the distance, Z, between the focal point of the bulb and the ground planenThe initial position of the nth frame image;
initial position Z of the n-th frame imagenObtained by the following formula:
Zn＝Zstart0-(n-1)×h0+(n-1)×Lp。
3. the X-ray image acquisition method according to claim 1, wherein when the rate of change of the image stitching run is equal to or less than a preset threshold, the actual exposure frame number is a maximum integer smaller than the initial exposure frame number.
4. The X-ray image acquisition method as claimed in claim 3, wherein when the actual exposure frame number is a maximum integer smaller than the initial exposure frame number, the height of the actual effective field in the corresponding actual gantry parameter is the height of the initial effective field, and the starting position Z of the actual effective field isstartAnd a termination position ZstopAre respectively obtained by the following formulas:
Zstart＝Zstart0-(L0-L1)/2；
Zstop＝Zstop0+(L0-L1)/2。
5. the method of claim 4, wherein said calculating the corresponding detector position at which each frame of image is acquired based on said actual exposure frame number and said actual gantry parameters is performed by the following equation:
ZFDn＝Zstart-((2n-1)/2)×h0+(n-1)×Lp；
wherein Z isFDnThe central position of a corresponding detector when the nth frame of image is collected, wherein n is the number of exposure frames; and calculating the corresponding bulb tube rotation angle when each frame of image is acquired based on the actual exposure frame number and the actual frame parameter by the following formula:
wherein alpha isRHAThe difference between the included angle between the axis of the bulb and the X axis when the bulb rotates on the XZ plane during the collection of the nth frame image and the included angle between the axis of the bulb and the X axis when the bulb rotates on the XZ plane during the collection of the (n-1) th frame image; arctan () is an arctangent function, SSIDIs the source image distance, ZTCSIs the distance, Z, between the focal point of the bulb and the ground planenThe initial position of the nth frame image;
initial position Z of the n-th frame imagenObtained by the following formula:
Zn＝Zstart-(n-1)×h0+(n-1)×Lp。
6. the X-ray image acquisition method as set forth in claim 1, wherein when the rate of change of the image stitching run is greater than a preset threshold, the actual exposure frame number is a maximum integer smaller than the initial exposure frame number plus 1.
7. The method of claim 6, wherein when the actual exposure frame number is the maximum integer of the initial exposure frame number plus 1, the start position of the actual effective field in the corresponding actual frame parameter is the start position of the initial effective field, the end position of the actual effective field is the end position of the initial effective field, and the height of the actual effective field is obtained by the following formula:
h＝Lp+(L0-Lp)/(floor(Y)+1)。
8. the method of claim 7, wherein said calculating the corresponding detector position at which each frame of image is acquired based on said actual exposure frame number and said actual gantry parameters is performed by the following equation:
ZFDn＝Zstart0-((2n-1)/2)×h+(n-1)×Lp；
wherein Z isFDnThe central position of a corresponding detector when the nth frame of image is collected, wherein n is the number of exposure frames; and calculating the corresponding bulb tube rotation angle when each frame of image is acquired based on the actual exposure frame number and the actual frame parameter by the following formula:
wherein alpha isRHAFor collecting the n-th frame image, the included angle between the axis of the bulb and the X axis when the bulb rotates on the XZ planeThe difference between the included angle of the axis of the bulb and the X axis when the bulb rotates on the XZ plane during the collection of the (n-1) th frame image; arctan () is an arctangent function, SSIDIs the source image distance, ZTCSIs the distance, Z, between the focal point of the bulb and the ground planenThe initial position of the nth frame image;
initial position Z of the n-th frame imagenObtained by the following formula:
Zn＝Zstart0-(n-1)×h+(n-1)×Lp。
9. an X-ray image acquisition apparatus characterized by comprising:
the first calculation unit is used for setting initial frame parameters and an overlapping area of two adjacent frames of images according to the pre-exposure area and calculating the number of initial exposure frames for image splicing; the rack parameters include: the beam limiting device comprises an initial position, an end position and the height of an effective light field, wherein the initial position and the end position of the effective light field at least comprise the heights of two effective light fields, and the height of the effective light field is related to the size of an opening of the beam limiting device in the vertical direction;
a first obtaining unit, configured to adjust the initial exposure frame number to obtain an actual exposure frame number, where when the initial exposure frame number is an integer, the actual exposure frame number is the initial exposure frame number; when the initial exposure frame number is a non-integer, the actual exposure frame number is related to the change rate of an image splicing process; determining actual frame parameters according to the actual exposure frame number, so that an actual exposure area is not larger than the pre-exposure area, and the absolute value of the difference between the actual exposure frame number and the initial exposure frame number is smaller than 1; the change rate of the image splicing stroke is related to an initial splicing stroke and a preset splicing stroke;
the second calculation unit is used for calculating the corresponding detector position and the bulb tube rotation angle when each frame of image is collected based on the actual exposure frame number and the actual frame parameter;
and the image acquisition unit is used for carrying out exposure according to the actual frame parameters, the corresponding detector position when each frame of image is acquired and the rotating angle of the bulb tube, and acquiring the images to be spliced.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201611267562.8A CN106852697B (en) | 2014-09-28 | 2014-09-28 | X-ray image acquisition method and device |
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201611267562.8A CN106852697B (en) | 2014-09-28 | 2014-09-28 | X-ray image acquisition method and device |
| CN201410508290.0A CN104287756B (en) | 2014-09-28 | 2014-09-28 | Radioscopic image acquisition methods and device |
Related Parent Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201410508290.0A Division CN104287756B (en) | 2014-09-22 | 2014-09-28 | Radioscopic image acquisition methods and device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN106852697A CN106852697A (en) | 2017-06-16 |
| CN106852697B true CN106852697B (en) | 2020-12-18 |
Family
ID=52307897
Family Applications (2)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201410508290.0A Active CN104287756B (en) | 2014-09-22 | 2014-09-28 | Radioscopic image acquisition methods and device |
| CN201611267562.8A Active CN106852697B (en) | 2014-09-28 | 2014-09-28 | X-ray image acquisition method and device |
Family Applications Before (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201410508290.0A Active CN104287756B (en) | 2014-09-22 | 2014-09-28 | Radioscopic image acquisition methods and device |
Country Status (1)
| Country | Link |
|---|---|
| CN (2) | CN104287756B (en) |
Families Citing this family (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| GB2553022B (en) | 2014-09-22 | 2018-12-05 | Shanghai United Imaging Healthcare Co Ltd | System and method for image composition |
| KR102377484B1 (en) * | 2015-04-20 | 2022-03-22 | 주식회사 바텍 | X-ray generating device having motionsensor and method for x-ray imaging using the same |
| CN107440735B (en) * | 2017-09-27 | 2020-10-02 | 上海联影医疗科技有限公司 | Method and system for initializing angle of CT scanning bulb tube |
| US11253221B2 (en) | 2017-06-01 | 2022-02-22 | Shanghai United Imaging Healthcare Co., Ltd. | Systems and methods for configuring medical device |
| CN108125687A (en) * | 2017-11-30 | 2018-06-08 | 佛山杰致信息科技有限公司 | A kind of medical imaging control system |
| CN112243359A (en) | 2018-05-28 | 2021-01-19 | 上海联影医疗科技股份有限公司 | System and method for taking X-ray images |
| CN108652653B (en) * | 2018-05-28 | 2022-03-25 | 上海联影医疗科技股份有限公司 | Method and device for shooting medical image, medical image system and storage medium |
| WO2019233422A1 (en) | 2018-06-04 | 2019-12-12 | Shanghai United Imaging Healthcare Co., Ltd. | Devices, systems, and methods for image stitching |
| CN109758170B (en) * | 2019-01-10 | 2023-02-10 | 北京东软医疗设备有限公司 | Exposure parameter adjusting method and device of X-ray imaging equipment |
| 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 |
| CN110192911B (en) * | 2019-05-09 | 2021-03-16 | 上海联影医疗科技股份有限公司 | Target point puncturing method and device, storage medium and computer equipment |
| 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 |
| 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 |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6097833A (en) * | 1993-11-26 | 2000-08-01 | U.S. Philips Corporation | Image composition method and imaging apparatus for performing said method |
| US20040247081A1 (en) * | 2003-06-03 | 2004-12-09 | Ge Medical Systems Global Technology Company, Llc | Methods and apparatus for multiple image acquisition on a digital detector |
| CN101756707A (en) * | 2009-12-31 | 2010-06-30 | 苏州和君科技发展有限公司 | Method for carrying out scanning reconstruction on long target object by using Micro-CT imaging system |
| CN102138803A (en) * | 2009-12-22 | 2011-08-03 | 富士胶片株式会社 | Radiation imaging system and assist apparatus for the same |
| CN102316806A (en) * | 2006-12-20 | 2012-01-11 | 卡尔斯特里姆保健公司 | Long length imaging using digital radiography |
-
2014
- 2014-09-28 CN CN201410508290.0A patent/CN104287756B/en active Active
- 2014-09-28 CN CN201611267562.8A patent/CN106852697B/en active Active
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6097833A (en) * | 1993-11-26 | 2000-08-01 | U.S. Philips Corporation | Image composition method and imaging apparatus for performing said method |
| US20040247081A1 (en) * | 2003-06-03 | 2004-12-09 | Ge Medical Systems Global Technology Company, Llc | Methods and apparatus for multiple image acquisition on a digital detector |
| CN102316806A (en) * | 2006-12-20 | 2012-01-11 | 卡尔斯特里姆保健公司 | Long length imaging using digital radiography |
| CN102138803A (en) * | 2009-12-22 | 2011-08-03 | 富士胶片株式会社 | Radiation imaging system and assist apparatus for the same |
| CN101756707A (en) * | 2009-12-31 | 2010-06-30 | 苏州和君科技发展有限公司 | Method for carrying out scanning reconstruction on long target object by using Micro-CT imaging system |
Also Published As
| Publication number | Publication date |
|---|---|
| CN104287756A (en) | 2015-01-21 |
| CN104287756B (en) | 2017-03-08 |
| CN106852697A (en) | 2017-06-16 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN106852697B (en) | X-ray image acquisition method and device | |
| CN107789001B (en) | Positioning method and system for imaging scanning | |
| JP7295917B2 (en) | X-ray equipment for medical diagnostic imaging | |
| JP7331008B2 (en) | Alignment of X-ray medical imaging equipment using the Frankfurt plane | |
| US20100290707A1 (en) | Image acquisition method, device and radiography system | |
| JP6801962B2 (en) | X-ray equipment for medical diagnostic imaging | |
| US7715524B2 (en) | Radiation image capturing apparatus | |
| KR101190801B1 (en) | X-ray computed tomography apparatus and the method thereof | |
| TW201542171A (en) | Automatic selected human portion identification and adjustment device for medical equipment | |
| CN1579331A (en) | Method and apparatus for imaging organ | |
| JP2013517045A5 (en) | ||
| KR20170015928A (en) | Medical image photographing and medical image correction method using depth camera | |
| CN114445497A (en) | Image positioning method, image positioning device, dynamic image generating method, dynamic image generating device, dynamic image generating system and storage medium | |
| CN111214251A (en) | Mobile X-ray apparatus for digital tomography | |
| JP2010268827A (en) | X-ray ct apparatus and method of controlling the same | |
| JP6076658B2 (en) | Medical image processing apparatus, X-ray diagnostic apparatus, and medical image processing program | |
| JP6649315B2 (en) | Aperture device for X-ray equipment | |
| JP6412936B2 (en) | Method for photographing a three-dimensional X-ray image | |
| KR102246090B1 (en) | Radiology apparatus with FOV enlargement function | |
| JP6518250B2 (en) | Positioning of partial volumes of anatomy | |
| KR102043357B1 (en) | A method for changing a scale of an image and an apparatus for the same | |
| KR20200120108A (en) | Radiology apparatus with FOV enlargement function | |
| JP2014188220A (en) | X-ray computer tomography apparatus | |
| JP2006000222A (en) | X-ray ct apparatus | |
| WO2012115089A1 (en) | Radiological image-capturing device and method |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| CB02 | Change of applicant information |
Address after: 201807 Shanghai city Jiading District Industrial Zone Jiading Road No. 2258 Applicant after: Shanghai Lianying Medical Technology Co., Ltd Address before: 201807 Shanghai city Jiading District Industrial Zone Jiading Road No. 2258 Applicant before: SHANGHAI UNITED IMAGING HEALTHCARE Co.,Ltd. |
|
| CB02 | Change of applicant information | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |