Abstract:
To improve accuracy of diagnosis by making image restoration possible for obtaining high definition images in accordance with positions for examination. 
     An image processing device includes: an image data input section for inputting image data obtained by using a detector to read a radiation ray applied from a radiation source and passed through a subject; a position input section for inputting a position for examination on the subject; a memory section for storing in advance image restoration parameters which correspond respectively to positions for examination on the subject; and a processing section for generating a restored image based on an image restoration parameter read from the memory section which corresponds to the position for examination on the subject that is input by the position input section and the image data that is input from the image data input section.

Description:
[0001]    This application is based on Japanese Patent Application NO. 2006-255574 filed on Sep. 21, 2006 with Japan Patent Office, the entire content of which is hereby incorporated by reference. 
       FIELD OF THE INVENTION 
       [0002]    The present invention relates to an image processing device and an image processing method. In particular, the present invention relates to an image processing device and image processing method in which restoration processing is performed for a radiographic image. 
       BACKGROUND OF THE INVENTION 
       [0003]    In the past, fine images have been desired for early discovery of focus of disease, diseased areas and lesions in radiographic image radiography. As a result, detection performance of the radiation detector used in radiography has been increased, but the scattered radiation that is generated in the subject is also detected and this causes the image to deteriorate. In particular, as shown in  FIG. 9 , the radiation source  100  can only have a fixed area, and thus when radiation beams are irradiated on the object  101 , a displacement occurs between the projection region A 1  resulting from the radiation ray emitted from the upper end of the radiation source  100  and the projection region A 2  resulting from the radiation ray emitted from the lower end of the radiation source  100 , and because there is a disparity in the luminance distribution of the edge portion, a blurred image was obtained. 
         [0004]    In recent years, it has been proposed that the point spread function (referred to as PSF hereinafter) that is computed based on the radiographing conditions is used as a image restoration parameter in restoration processing to thereby restore blurred images and thus high definition images in which blurring is reduced are obtained (See Japanese Patent Publication No. 2509181 and Japanese Patent Publication No. 3423828 for example). 
         [0005]    In Japanese Patent Publication No. 2509181, a radiographic image radiographing system is described in which PSF which shows the scattered X-ray distribution on the detector surface for the X-rays irradiated onto the subject is corrected in accordance with radiographing conditions for the X-ray images and the filter coefficient is output. This filter coefficient and the original X-ray image are subjected to convolution to obtain a scattered X-ray image, and the scattered X-ray image is taken from the original X-ray image to directly obtain X-ray image. 
         [0006]    In addition, in Japanese Patent Publication No. 3423828, a radiographic image system is described in which an intensity spread function is obtained by multiplying the intensity ratio of the dispersed light in the state where there is no subject for detection by the PSF of the dispersed light and then calculating the image of the dispersion light components. Furthermore, the intensity spread function of the scattered radiation is obtained by multiplying the PSF of the scattered radiation in a state where there is a dummy human body subject which has approximately even thickness by the intensity ratio of the scattered light obtained from image of the subject and the radiographing conditions, and the image of the scattered radiation component is computed. By subtracting the image for the diffused light component and the image for the scattered radiation component from the image of the subject, deterioration restoration of the X-ray radiographic image is performed. 
         [0007]    However, because in performing examinations, each patient has different lesion sites and different organs for examination, as described in Japanese Patent Publication No. 2509181 and Japanese Patent Publication No. 3423828 and, even in the blurred image is restored using preset image restoration parameters that are computed based on radiographing conditions, depending on the location, blurring may not be reduced and there was a concern that accurate diagnosis was difficult. 
         [0008]    That is to say, when the positions for examination in the thickness direction of the subject in each patient differ, the point spread function for the X-ray passed through each subject for examination is different and thus the image restoration parameters for deterioration restoration of blurred image of the subjects to be examined also differ, and in the deterioration restoration process which uses one image restoration parameter, there was a problem in that X ray radiographic image of each subject for examination could not be accurately subjected to deterioration restoration. 
       SUMMARY OF THE INVENTION 
       [0009]    An object of the present invention is to provide an image processing device and an image processing method which is capable of image restoration for obtaining high definition images in accordance with the position for examination. 
         [0010]    (1) According to an image processing device reflecting an aspect of the present invention, the image processing device comprises: an image data input section for inputting image data obtained by using a detector to read a radiation ray applied from a radiation source and passed through a subject; a position input section for inputting a position for examination on the subject; a memory section for storing in advance image restoration parameters which correspond respectively to positions for examination on the subject; and a processing section for generating a restored image based on an image restoration parameter read from the memory section which corresponds to the position for examination on the subject that is input by the position input section and the image data that is input from the image data input section. 
         [0011]    (2) According to another aspect of the invention, in the image processing device of Item 1 wherein, wherein the position input section is adapted to selectively input the position for examination in a direction of the radiation ray applied from the radiation source, and the memory section stores image restoration parameters based on point spread functions which correspond respectively to the positions for examination on the subject. 
         [0012]    (3) According to still another aspect of the present invention, in the image processing device of Item 1 or Item 2, the image processing device further comprising: an image restoration parameter generating section which generates image restoration parameters based on reference image data corresponding to preset positions for examination input from the image data input section. 
         [0013]    (4) According to an image processing method reflecting another aspect of the present invention, the method comprises: inputting image data obtained by using a detector to read radiation ray that is applied from a radiation source and passed through an subject; inputting a position for examination on the subject; reading an image restoration parameter corresponding to the position for examination on the subject that was selected in the position input step among image restoration parameters that are stored in advance corresponding to each position for examination on the object; and generating a restored image based on the image restoration parameter that has been read in the reading step and the image data that has been input at the image data input step. 
         [0014]    (5) According to still another aspect of the present invention, in the image processing method recited in Item 4, the position input step performs selective input of the position for examination in a direction of radiation ray applied from the radiation source, and the image restoration parameter read in the reading step is based on a point spread function which corresponds to the position for examination on the object. 
         [0015]    (6) According to yet another aspect of the present invention, in the image processing method recited in Item 4 or Item 5, the image processing method further comprises: inputting reference image data that is linked to preset positions for examination; and generating the image restoration parameters based on reference image data input in the reference image input step and links the image restoration parameters with the positions for examination and stores them. 
         [0016]    According to the present invention, image restoration parameters corresponding to each position for examination are stored in advance in the memory section, and thus the parameters corresponding the positions for examination are read from the memory section and if restored images are generated using the image restoration parameters and the image data, even if the positions for examination are different, fine images can be restored. As a result, it becomes possible to perform diagnosis with high accuracy at any position for examination. 
     
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         [0017]      FIG. 1  is a side view showing the schematic structure of a radiographic image radiographing system including the image processing device of this embodiment. 
           [0018]      FIG. 2  is a block diagram showing the main control structure of the image processing device of  FIG. 1 . 
           [0019]      FIG. 3  is an explanatory diagram showing the operation screen displayed in operation section included in the image processing device of  FIG. 2 . 
           [0020]      FIG. 4  is an explanatory drawing showing the device structure for obtaining image data for obtaining PSF 
           [0021]      FIG. 5  is an explanatory diagram showing the positions for examination in the chest area and the abdomen area. 
           [0022]      FIG. 6  is graph showing a specific example of PSF. 
           [0023]      FIG. 7  is a flowchart of an image processing method that is performed in the image processing device of  FIG. 2 . 
           [0024]      FIG. 8  is an explanatory diagram showing the flow of the restoration process. 
           [0025]      FIG. 9  is an explanatory diagram showing the principle for generating blurred images using the radiation source of the prior art. 
       
    
    
     DESCRIPTION OF THE PREFERRED EMBODIMENT 
       [0026]    The following is a description of the image processing device of this embodiment with reference to the drawings.  FIG. 1  is an explanatory diagram showing the schematic structure of a radiographic image radiographing system including the image processing device. As shown in  FIG. 1 , the radiographic image radiographing system  1  comprises an X-ray source  2  which irradiates X-rays as radiation and a radiographing device  3  which radiographs X-ray images for the subject H using X-rays that have been irradiated from the X-ray source  2  and passed through the subject H. 
         [0027]    The radiographing device  3  comprises a radiographing section  32  which includes a detector  31 , a main body  33  for performing radiographing control and the like. 
         [0028]    The radiographing section  32  has a built-in detector  31  and is formed such that its height position can be adjusted to match the radiographing site. 
         [0029]    The detector  31  detects radiated X-rays and is arranged so as to oppose the X-ray source  2 . A phosphorescent plate or FPD (flat panel detector) which can absorb and store X-ray energy is used as the detector  31 . For example, in the case where a phosphorescent plate is used, a reading section in which excitation light such as a laser beam or the like is irradiated on the phosphorescent plate and the phosphorescent light that is radiated from the phosphorescent plate is photoelectrically converted to image signals is provided in the radiographing section  32 . The image signal (analog signal) generated by the reading section is output to the main body  33 . 
         [0030]    Meanwhile, the FDP has conversion elements arranged in a matrix which generate electric signals in accordance with the amount of X-rays input and is different from the phosphorescent plate in that electric signal are generated directly in the FDP. For example, in the case where FPD is used as the detector  31 , the electric signals generated in the FPD are subjected to A/D conversion and the obtained digital image data is output to the main body section  33 . 
         [0031]    The main body section  33  is connected to the radiographing section  32  and has loaded an image processing device  10  which performs image processing for the image signals or the digital image data input from the detector  31 . 
         [0032]      FIG. 2  is a block diagram showing the main control configuration of the image processing device  10 . As shown in  FIG. 2 , the image processing device  10  comprises: an image data input section  11  in which image data (image signal or digital image data) read at the detector  31  is input; an operation section  12  in which various commands are input; a memory section  13  which stores various control data and image data; a processing section  14  which performs image processing for the image data based on the control data in the memory section  13 ; an output section  15  which outputs image data that was subjected to image processing to an external display device  60 ; and a control section  16  which controls all these sections. 
         [0033]    The image data input section  11  is electrically connected to the detector  31  and allows input of the image data that is read at the detector  31 . 
         [0034]    The operation section  12  is formed from a known touch panel type operation panel for example, and the radiographing start command, the restored image generate command, the radiographing conditions, the positions for examination and the like are input by operations by the user. In addition, the operation section  12  functions as the input section of the present invention which selects the position for examination of the subject H. When the position for examination of the subject H is to be selected, an operation screen with a model of the subject such as that shown in  FIG. 3  for example is displayed in the operation section  12 . The screen  120  is displayed so as to be divided into the chest area  121  (right surface side P 11 , middle surface side P 21 , left surface side P 31 , right center P 41 , middle center P 51 , left center P 61 , right bottom side P  71 , center bottom side P 81 , left bottom side P 91 ), and the abdomen area  122  (right surface side P 12 , center surface side P 22 , left surface side P 32 , right center P 42 , middle center P 52 , left center P 62 , right bottom side P  72 , center bottom side P 82 , left bottom side P 92 ), and selective input of the positions for examination is done by touching those positions. 
         [0035]    In the memory section  13  the PSF (point spread function) for example is used as the image restoration parameter and it is linked with the position for examination and stored. The PSF is the function used when restoring a blurred image. The image restoration process is described hereinafter. The PSF is set for each position for examination and these PSFs are stored in advance in the memory section  13 . 
         [0036]    The processing section  14  reads the PSF corresponding to the position for examination on the subject H selected at the operation section  12  from the memory section  13  and the restored image is generated based on the PSF and the image data that was stored in the memory section  13 . 
         [0037]    The control section  16  can perform command operations for the tube voltage, X-ray radiation conditions or radiation timing for tube current X-ray in the X-ray source  2  based on the command put in the operation section  12  and in the control section  16 , central control of the operation of the X-ray source  2  and the radiographing section  32  is performed in accordance with the command operations. 
         [0038]    The computing process for the PSF that is stored in the memory section  13  and linked to the positions for examination that can be selectively input at the operation section  12 , namely, the image restoration parameter generation process will be described next. The computing process of the PSF is performed before object radiography (for example, when installing the device, when maintenance is done, when the X-ray source or the detector  31  is replaced) and is performed for each position for examination. As shown in  FIG. 4 , in the computing process for PSF, the radiation source is formed of a material such as lead and the like which shields radiation, and a phantom PH having plurality of plate materials  50  in which a penetration hole  51  is formed and arranged at prescribed positions is used. The thickness of the plate material  50  is 0.01-0.1 mm, and the diameter of the penetration hole  51  is between a few μm and 50 μm. In the phantom PH each plate material  50  is arranged at a location corresponding to a position for examination at the time of radiographing the object. For example in  FIG. 4 , the case is shown in which a plate material  50  is arranged at each of the positions for examination (right surface side P 11 , middle surface side P 21 , left surface side P 31 , right center P 41 , middle center P 51 , left center P 61 , right bottom side P  71 , center bottom side P 81 , left bottom side P 91 ) of the chest area and abdomen area. It is to be noted that  FIG. 4  is a view of phantom PH from above, while  FIG. 5  is a view of phantom PH from the arrow X direction of  FIG. 4 , and they show the positions for examination of the chest area (right surface side P 11 , middle surface side P 21 , left surface side P 31 ) and the abdomen area (right surface side P 12 , middle surface side P 22 , left surface side P 32 ). 
         [0039]    In addition, when the PSF for the positions for examination is obtained, it is preferable that the plate materials  50  are arranged so that they do not overlap in the direction of radiation from the X-ray source in order to prevent the image sharpness for the plate material from being limited due to other plate materials  50  that are not involved. That is to say, in this embodiment, the plate materials  50  corresponding to the positions for examination at the surface side, the center and the bottom side are radiographed individually for the surface side, the center and the bottom side. It is to be noted that plate material  50  may be sequentially arranged at each of the positions for examination and radiography may be performed at each. 
         [0040]    The flow for the PSF calculation process will be described in the following. The user places the phantom PH at the same position as the position for radiographing object H in the radiographing device  3  and then inputs the PSF generation start command. When this is input, the control section  16  controls the X-ray source  2  and the radiographing section  32  and the image in the penetration hole  51  in the plate material  50  that is placed on the phantom PH is radiographed and the obtained reference image data is input to the image data input section  11  from the radiographing section  32  (reference image data input step). When the reference image data is input from the image data input section  11 , the control section  16  generates luminance distribution from the image data, and a function which is similar to the linear form of the luminance distribution is formed. The function that is formed is the PSF of the positions for examination. 
         [0041]    PSF is a spread function such as that shown in  FIG. 6 .  FIG. 6  shows a PSF in which the amount of displacement on the image receiving surface of the detector  31  when the center position of the penetration hole  51  is shown as 0 on the horizontal axis and the maximum value for the intensity of the radiation ray that is detected in the displacement amount is shown as 1.0 on the vertical axis. In  FIG. 6 , A shows the PSF for the positions for examination closest to the detector  31  (60 mm from the surface of the detector  31 ) and C shows the PSF for the positions for examination closest to the X-ray source  2  (260 mm from the surface of the detector  31 ). It is to be noted that PSF shown in  FIG. 6  is computed based on a focal diameter of 500 μm for the X-ray radiation source, a distance of 650 mm from the X-ray radiation source  2  to the detector  31 , and reference image data at a diameter of 10 μm for the penetration holes  51 . 
         [0042]    In A of  FIG. 6 , there is little blurring effect caused by the focal diameter of the X-ray source  2  and the distribution of the radiation rays is narrow. On the other hand, in C of  FIG. 6 , there is large blurring effect caused by the focal diameter of the X-ray source  2  and the distribution of the radiation rays is wide. That is to say, in the case of the positions for radiation that are close to the detector  31 , restoration parameters with little blurring effect caused by the focal diameter are used and in the case of positions that are separated from the detector  31 , restoration parameters with a large blurring effect caused by the focal diameter are used and thus favorable image restoration becomes possible. 
         [0043]    It is to be noted that in this embodiment, PSF corresponding to blurring caused by focal diameter is used, but in addition to blurring caused by focal diameter, PSF including blurring caused by scattered radiation inside the object may also be used. 
         [0044]    It is to be noted in the case where image data of the penetration holes  51  in the multiple plate materials  50  is included, in the image data of a single radiography it is preferable that the image data is divided into single image data for each plate material  50  and penetration hole  51  and then the luminance distribution each of the images for the penetrations holes  51  is generated. The PSF that is generated are linked with the positions for examination and stored in the memory section  13 . This process is repeated until the PSF of all the positions for radiation are generated. 
         [0045]    Next, the image processing method of the present invention that is performed using the radiographic image radiographing system  1  of the present invention will be described.  FIG. 7  is a flowchart showing an image processing method. When the user inputs a radiography start command by operating the operation section  12 , the control section  16  controls the X-ray source  2  and the radiographing section  32  and the image H is radiographed and the obtained image data is input into the image data input section  11  from the radiographing section  32  (Step S 1 : image data input step). 
         [0046]    In Step S 2 , the control  16  stores the image data input to the image data input section  11  in the memory section  13 . 
         [0047]    In Step S 3 , the control section  16  determines whether the restored image creation command has been input to the image data input section  11 , and if it has been input the process moves to Step S 4 , while if it has not been input, it moves to Step S 7 . 
         [0048]    In Step S 4 , the positions for examination are selectively input by the operation section  12  using the operation screen  120  shown in  FIG. 3 , and moves to Step  5 . 
         [0049]    In Step S 5 , the control section  16  reads the PSF corresponding to the positions for examination selected by the operation section  12  and the image data obtained by radiographing from the memory section  13  (readings step) and moves to Step S 6 . 
         [0050]    In Step S 6 , the control section  16  generates a restored image based on the read PSF and the image data (processing step) and moves to Step S 7 . 
         [0051]    In Step S 7 , the control section  16  performs image processing other than restoration processing for unrestored image data or restored image data then moves to Step S 8 . 
         [0052]    In Step S 8 , the control section  16  controls the output section  15  and outputs image data that has been subjected to image processing in Step S 7  to an external device  60  and the process ends. 
         [0053]    The restored image creation process performed in Step S 6  will be described using  FIG. 8 .  FIG. 8  is an explanatory diagram showing the flow of the restored image creation process. When the image data for the object H that was read from memory  13  is input (Step S 61 ), the processing section  14  performs Fourier transformation of the image data (Step S 62 ). Subsequently, the processing section  14  reads the PSF from the memory section  13  (Step S 63 ) and then the PSF that was read is subjected to Fourier transformation (Step S 64 ). Subsequently, the processing section  14  divides the image data that was subjected to Fourier transformation in Step S 62  by the PSF that was subjected to Fourier transformation in Step S 64  (Step S 65 ) and then the result of the calculation was subjected to inverse Fourier transformation (Step S 66 ), and the restored image (image data for restored image) is generated. 
         [0054]    It is to be noted that it is preferable to carry out the equation below based on Bayes estimation rather than simply by deconvolution. In equation (2), H is X-ray projection image, W is the restored deteriorated image and S is PSF. Also, in equation (2), a=(1, k−K+1) max , b=(k,I) min . K is the element number of the vector S and I is the element number of the vector W and k={1, 2, . . . , K} and i={1, 2, . . . , I}. r is an integer greater than 0 which shows the repetition frequency. 
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         [0055]    According to the above embodiment, the PSF corresponding to each of the positions for examination are stored in advance in the memory section  13  and thus the PSF corresponding to the positions for examination are read from the memory section  13  and restored images are generated using the PSF along with the image data, even if the positions for examination are different, fine images can be restored. As a result, it becomes possible to perform diagnosis with high accuracy at any position for examination. 
         [0056]    In addition, in the image processing device  10  of this embodiment, the position for examination can be selectively input in the direction of radiation of the radiation rays, and in particular, it becomes possible to generate fine restored images in which consideration is given to the point spread function caused by the focal diameter of the x-ray source  2 . 
         [0057]    Also, according to this embodiment, the image restoration parameters are generated based on reference image data that has been linked in advance with positions for examination and stored and thus it becomes possible to generate restored images in accordance with individual difference between the X-ray source  2  and the radiographing device  3 . 
         [0058]    It is to be noted that the present invention is, as a matter of course not limited to the above embodiment and suitable modifications are possible. 
         [0059]    For example, in this embodiment, images in which the object is divided for each of the positions for examination are displayed at the operation section  12  and thus the example is described in which the positions for examination can be selected but the coordinates for the positions for examination may be directly input to thereby select the positions for examination. In this case the reference point for the coordinates may for example be such that the center and Z coordinates (depth direction) of the detector  31  at the X coordinate (horizontal direction) and Y coordinate (vertical direction) is the surface of the detector  31 . 
         [0060]    In addition, in this embodiment, the case where the PSF for positions for examination is generated and used in the restoration process, but the PSF is preferably generated corresponding not only to each position for examination but also to the X-ray source  2  and the detector  31 . For example, if the PSF for each position for examination is generated immediately after replacement of the X-ray source  2  and the detector  31 , it becomes possible to generate PSF for each position for examination corresponding to the X-ray source  2  and the detector  31  as well. As a result, PSF can be generated in which the individual difference of the X-ray source  2  and the detector  31  are taken into consideration and more favorable restoration processing becomes possible.