JP2007244738A - Medical image system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To display a photographed image in such a way that a doctor can easily and efficiently discriminate asbestos shadows in the image. <P>SOLUTION: In the medical image system 100, the normal photography for photographing the whole chest region of a subject and the enlarging photography for a part of the chest region is switched in the photography by a photography device 10. After the photography, an image generating device 3 generates data on the whole image photographed by the normal photography and data on the chest image photographed by the enlarging photography. An image processing device 20 processes the whole image for image reading, and processes the partial image for image reading and for detecting asbestos shadows. A display device 50 displays the whole image processed for image reading and the partial image processed for image reading or for detecting asbestos shadows in a display part in such a state as correlated with each other according to the display control by a control part. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention relates to a medical image system that captures and displays a chest image of a subject's chest.

  In recent years, asbestos that has entered the human body has become a problem as it induces serious diseases such as pneumoconiosis and mesothelioma. For this reason, an examination for taking a chest X-ray image of a patient and detecting the presence or absence of asbestos in the human body from the X-ray image is performed. Detection of asbestos is expected to lead to rapid treatment (treatment, preventive measures) and suppress disease.

  However, with a general X-ray imaging method performed in a normal inspection, it is difficult to visualize a fine structure having a diameter of about 10 μm or less such as asbestos. Even if a visible image can be formed, the visibility is low and the doctor cannot often observe (discriminate). This is because the size of the structure to be imaged is larger than the spatial resolution of the image detector used in X-ray imaging. This is because is small.

  In order to obtain an X-ray image capable of finely observing a minute object such as asbestos, enlargement photography is effective. In the magnified photographing, the X-ray image is enlarged more than the actual size of the subject by setting the focal diameter of the X-ray tube, the distance from the X-ray tube to the subject, and the distance from the subject to the image detector as a predetermined relationship. Is the way to get.

2. Description of the Related Art Conventionally, an imaging system that can switch between such enlarged imaging and general normal imaging for imaging the abdomen and the like has been disclosed (see, for example, Patent Document 1).
JP-A-2005-270201

In many cases, a captured image is displayed after various image processing such as gradation processing and sharpness adjustment processing is performed so as to improve visibility during interpretation.
However, in magnified shooting, an image having a density characteristic different from that in normal shooting can be obtained due to the difference in shooting method. Therefore, even if image processing similar to that in normal shooting is performed, the visibility of asbestos is not improved.
Therefore, if the same image processing is performed uniformly as before, even if the processed image is provided to the doctor, it seems that the efficiency of the doctor's asbestos shadow interpretation work cannot be expected.

  The subject of this invention is displaying a picked-up image so that a doctor can discriminate | determine the asbestos shadow in a picked-up image easily and efficiently.

The invention according to claim 1 is a medical image system,
Photographing means for switching between normal photographing for photographing the entire chest of the subject and enlarged photographing for a part of the chest;
Data generating means for generating data of the whole image shot by the normal shooting and the partial image of the chest shot by the enlarged shooting;
First image processing means for performing first image processing including image processing for interpretation on the entire image;
Second image processing means for performing second image processing including image processing for image interpretation and image processing for asbestos shadow detection on the partial image;
Display means for performing image display;
Control means for associating and displaying the entire image subjected to the first image processing and the partial image subjected to the second image processing on the display means;
It is characterized by providing.

The invention according to claim 2 is the medical image system according to claim 1,
The control means displays the whole image subjected to the first image processing and the partial image subjected to the second image processing on the same screen.

The invention according to claim 3 is the medical image system according to claim 1,
The image processing for image interpretation includes one or more of gradation conversion processing or frequency enhancement processing,
The image processing for detecting asbestos shadow includes one or more of gradation conversion processing, frequency enhancement processing, and gradation inversion processing.

The invention according to claim 4 is the medical image system according to any one of claims 1 to 3,
Comprising an operation means for performing an instruction operation of display contents in the display means;
The control means switches between a partial image subjected to the image processing for interpretation and a partial image subjected to the image processing for asbestos detection in accordance with an instruction operation by the operation means. Features.

The invention according to claim 5 is the medical image system according to any one of claims 1 to 3,
The control unit is configured to identify and display a position corresponding to the partial image in the entire image displayed on the display unit.

The invention according to claim 6 is the medical image system according to claim 5,
Comprising an operation means for performing an instruction operation of display contents in the display means;
When the partial image is selected and operated through the operation unit, the control unit displays a position corresponding to the selected partial image in the entire image.

The invention according to claim 7 is the medical image system according to claim 5,
Comprising an operation means for performing an instruction operation of display contents in the display means;
The control means is characterized in that when a portion corresponding to the partial image in the whole image is selected and operated via the operation means, the partial image of the selected portion is identified and displayed.

  According to the first aspect of the present invention, the whole image is for interpretation, and the doctor can observe the whole image and the partially enlarged image for the same patient. In addition, since the partial image is subjected to image processing for interpretation or asbestos shadow detection, the whole image is used for overall observation, and the image for interpretation having an edge effect is used for partial observation. Multiple images that have undergone image processing suitable for the purpose of interpretation, such as partial images that have undergone image processing, and partial images that have undergone image processing for asbestos detection, if you want to perform interpretation specifically for asbestos shadows It can be used for interpretation in combination. Therefore, when visually detecting a minute shadow such as an asbestos shadow, the doctor can easily and efficiently detect the asbestos shadow.

  According to the second aspect of the present invention, the doctor can interpret the entire image and the partial image while comparing them. Interpretation efficiency can be improved by combining and observing the entire image and the partial image.

  According to the third aspect of the present invention, it is possible to perform image processing suitable for interpretation by gradation conversion processing, frequency enhancement processing, and gradation inversion processing, or image processing for improving the visibility of asbestos shadows.

  According to the invention described in claim 4, image processing for image interpretation is performed, and a partial image in which the edge of the subject is clear due to the edge effect and image processing for asbestos detection are performed. The partial image in which the asbestos shadow is emphasized can be easily switched and observed according to the purpose of interpretation.

  According to the fifth aspect of the present invention, the doctor can easily identify which part of the whole image corresponds to the partial image.

  According to the sixth aspect of the present invention, the doctor can identify the position in the whole image corresponding to the partial image only by selecting the partial image to be observed. Therefore, it is possible to easily grasp the positional relationship with respect to the entire partial image.

  According to the seventh aspect of the present invention, the doctor can select which image is the partial image corresponding to the portion only by selecting and operating the portion to be enlarged and observed in the entire image to be observed. Can do. Therefore, it is possible to grasp a partial image of a portion that is desired to be easily observed.

First, the configuration will be described.
FIG. 1 shows a configuration of an X-ray imaging system 100 in the present embodiment.
As shown in FIG. 1, the X-ray imaging system 100 includes an imaging device 10, an image processing device 20, a film output device 30, an image server 40, and a display device 50. Each of the devices 10 to 50 is a network. N is connected. The network N is a LAN (Local Area Network) compliant with DICOM (Digital Imaging and Communication in Medicine) standards.

  In the X-ray image system 100, when digital data of an X-ray image is generated by irradiating the chest of the subject with the X-ray imaging apparatus 10, various image processes are performed on the X-ray image by the image processing apparatus 20. The processed image output from the image processing device 20 is stored in the image server 40 and output to the film output device 30 or output to the display device 50 in response to a request from the display device 50.

Hereinafter, each component device will be described.
As shown in FIG. 2, the imaging apparatus 10 includes an X-ray source 2 and an image generation apparatus 3, and X-rays emitted from the X-ray source 2 toward the subject W are included in the image generation apparatus 3. It is detected by the image detector 31, and digital data of an X-ray image corresponding to the X-ray dose is generated.

  The X-ray source 2 generates X-rays and irradiates the subject W. In the X-ray source 2, two types of X-ray sources 21 and 22 (see FIG. 3) are installed to be switchable. The X-ray source 21 has an X-ray tube with a focal diameter D1 (μm) prepared for normal imaging. The X-ray source 22 has an X-ray tube having a focal diameter D2 (μm) prepared for phase contrast imaging, which is one type of magnification imaging. At the time of imaging, it is possible to switch between normal imaging and enlarged imaging by switching the X-ray sources 21 and 22.

  Here, the normal photographing means a photographing method in which the image detector 31 is arranged at a position in contact with the subject W as shown in FIG. In this case, since the X-ray that has passed through the subject W is immediately received by the image detector 31, the X-ray image has substantially the same size as the life size (which means the same size as the subject W).

  On the other hand, magnified shooting refers to a shooting method in which a distance is provided between the subject W and the image detector 31 as shown in FIG. In this case, since the X-ray irradiated from the X-ray source 2 in the shape of a cone beam passes through the subject W and then enters the image detector 31 in the shape of a cone beam, the obtained X-ray image is compared with the life size. The enlarged size. This enlarged image is called an enlarged image.

The enlargement ratio M with respect to the life size of the enlarged image is R1 from the X-ray source 2 to the subject W, R2 from the subject W to the image detector 31, and the distance from the X-ray source 2 to the image detector 31. When R3 (R3 = R1 + R2), it can be obtained by the following formula (1).
M = R3 / R1 (1)

The enlargement ratio M can be adjusted by increasing or decreasing the distances R1 and R2.
When the setting of the distance R3 is limited, such as in a shooting room, the distance R3 is fixed, and the ratio of the distances R1 and R2 may be changed within the fixed distance R3.

In the present embodiment, in the above-described magnified shooting, the setting of R1, R2, R3 and the focal diameter D2 as disclosed in Japanese Patent Laid-Open No. 2001-91479 is set within a predetermined range, so that the object side Employs phase-contrast imaging that provides an edge enhancement effect.
In the phase contrast image obtained by the phase contrast imaging, the X-rays refracted by passing through the edge of the subject W overlap with the X-rays passed without passing through the subject W, and the X-ray intensity of the overlapped portion is increased. A phenomenon occurs. On the other hand, a phenomenon occurs in which the X-ray intensity is weakened in the inner portion of the edge of the subject W by the amount of refracted X-rays. Therefore, an edge enhancement function (also referred to as an edge effect) in which an X-ray intensity difference is widened at the border of the subject W works, and a highly visible X-ray image in which the border portion is sharply drawn is obtained. Become.

When the X-ray source 2 is regarded as a point source, the X-ray intensity at the edge portion is as shown by the solid line in FIG. E shown in FIG. 4 indicates the half-value width of edge emphasis and can be obtained by the following equation (2). The half-value width E indicates the distance between the peaks and valleys of the edge.

  However, in medical sites and non-destructive inspection facilities, Coolidge X-ray tubes (also called thermoelectron X-ray tubes) are widely used as X-ray sources, and this Coolidge X-ray tube has a large focal diameter. Cannot be considered as a point source. In this case, a half-width E for edge enhancement is widened and a geometrically unsharp phenomenon occurs in which the intensity is reduced, and the X-ray intensity as shown by the dotted line in FIG. 4 is obtained. This geometrical sharpness is called blur.

式中、δ及びｒの定義は式２と同じである。
また、ＥＢはボケが無い場合のエッジ強調半値幅Ｅにボケの大きさを示すＢを加え、ＥＢ＝Ｅ＋Ｂで示される。 If the half-value width of edge enhancement when blur occurs is EB, EB can be obtained from the following equation (3).

In the formula, the definitions of δ and r are the same as those in the formula 2.
EB is represented by EB = E + B by adding B indicating the size of the blur to the edge emphasis half width E when there is no blur.

  As described above, as the focal diameter of the X-ray source 2 is smaller, the blur is reduced and the obtained edge effect is increased. Therefore, the X-ray sources 21 and 22 are prepared as D1> D2, and the X-ray source 22 having a smaller focal diameter D2 than the focal diameter D1 used for normal imaging is used for magnified imaging of fine asbestos shadows.

  Further, the X-ray source 2 is configured so that its position can be moved vertically and horizontally. By moving the position of the X-ray source 2, the irradiation center position of X-rays irradiated in a cone beam shape (this is called a target) can be freely changed. The target is the center position of the photographed image obtained by photographing.

  As shown in FIG. 5A, when normal imaging is performed with the entire chest as the imaging range to obtain an entire image T of the chest, and when enlarged imaging is performed with the portions P1 and P2 of the chest as the imaging range, Is as shown in FIG.

  In normal imaging for imaging the entire chest, as shown in FIG. 5B, the center of the chest (in the figure, the center is indicated by a cross marker) is used as a target for X-ray irradiation, whereas in enlarged imaging, The target needs to be aligned with the center of the part to be enlarged. The amount of movement and the direction of movement of the X-ray source 2 associated with the change of the target are determined in a relative positional relationship with respect to the target for normal imaging. When the target position is changed, the position of the X-ray source 2 is moved according to the movement amount and movement direction stored in advance.

  For example, if the position coordinate of the target position for normal shooting is the origin (0, 0), when switching from normal shooting to enlarged shooting of the portion P1, the center (x1, y1) of the portion P1 from the current position (0, 0) The target position is changed to the position of). The amount of movement of the X-ray source 2 is x1 in the X direction and y1 in the Y direction. Next, when switching from the enlarged shooting of the portion P1 to the enlarged shooting of the portion P2, the target position is changed from the current position (x1, x2) to the position of the center (x2, y2) of the portion P2. The amount of movement of the X-ray source 2 is (x2-x1) in the X direction and (y2-y1) in the Y direction.

As shown in FIG. 2, the image generation apparatus 3 includes an imaging unit 32 including an image detector 31, a main body unit 33 for performing imaging control, and the like.
The imaging unit 32 includes an image detector 31 and is configured to be able to adjust the height position according to the imaging region.

  The image detector 31 detects irradiated X-rays. As the image detector 31, a volatile phosphor plate capable of absorbing and storing X-ray energy, an FPD (Flat Panel Detector), or the like can be applied. When a volatile phosphor plate is applied, a reading unit that irradiates the luminescent phosphor plate with excitation light such as laser light and photoelectrically converts the stimulated light emitted from the phosphor plate into an image signal is photographed. It is provided in the part 32. The image signal (analog signal) generated by the reading unit is output to the main body unit 33.

  When a cassette in which a phosphor plate is housed in the housing is used as the image detector 31, image signal reading processing and digitization are performed using a cassette-dedicated reading device.

  On the other hand, the FPD has a conversion element that generates an electrical signal in accordance with an incident X-ray dose and is arranged on a matrix, and differs from the phosphor plate in that an electrical signal (analog) is directly generated in the FPD. . When the FPD is applied, an electrical signal generated in the FPD is converted into a digital signal by sampling and output to the main body 33.

  The main body unit 33 is connected to the X-ray source 2, an operation unit for performing control operations of imaging operations of the X-ray source 2 and the imaging unit 32, various signal processing such as converting image signals into digital data, A processing unit that performs data processing, a control unit that centrally controls each unit of the image generation apparatus 3, a communication unit that communicates with other external devices, and the like are provided.

  In the main body 33, it is possible to instruct the X-ray irradiation conditions such as tube voltage and tube current in the X-ray source 2 and the irradiation timing through the operation unit, and the control unit responds to this instruction operation. Centralized control of the operation of each unit such as the X-ray source 2 and the imaging unit 32 is performed.

  The image processing device 20 performs various image processing on the captured image generated by the imaging device 10. As shown in FIG. 6, the image processing apparatus 20 is a computer including a control unit 21a, an operation unit 22, a display unit 23, a communication unit 24, a storage unit 25, an image memory 26, an image processing unit 27, and the like. Various image processing is realized by the cooperation of the processing program and the control unit 21a.

  The control unit 21a includes a CPU (Central Processing Unit), a RAM (Random Access Memory), and the like, reads various control programs stored in the storage unit 25 by the CPU, expands them in the RAM, and performs various operations and each unit according to these programs. Centralized control is performed.

The operation unit 22 includes a mouse, a keyboard, and the like, generates an operation signal corresponding to these operations, and outputs the operation signal to the control unit 21a.
The display unit 23 includes a display and displays various display screens according to the control of the control unit 21a.

The communication unit 24 includes a communication interface such as a network interface card, and communicates with an external device on the network N.
The storage unit 25 stores various programs executed by the control unit 21a, image processing programs executed by the image processing unit 27, parameters and data necessary for the execution, and the like.

  The image memory 26 is a memory for storing a captured image to be processed and a processed image after processing.

  The image processing unit 27 executes various image processing according to the image processing program. As image processing, it is possible to perform various image processing such as gradation conversion processing, frequency enhancement processing, and gradation inversion processing after performing irradiation field recognition processing and region of interest setting as preprocessing. In addition, the image processing unit 27 performs a detection process of detecting a candidate area for an asbestos shadow by performing image analysis of a captured image or a processed image.

First, after describing the characteristics of the asbestos shadow appearing on the photographed image, each image processing will be described.
Human structures are mainly composed of elements such as C, H, O, and Ca, while asbestos is mainly composed of elements such as Si, O, Fe, and Mg. The relationship between each constituent element and its X-ray absorption rate is as shown in Table 1 below.

  Asbestos is often inhaled through the mouth and present in the alveoli. The alveolar constituent elements are mainly C, H, O, N and the like, and the difference is 10 times or more when the X-ray absorption rate is compared with Si which is the main component of asbestos. Therefore, when the same X-ray dose is irradiated on the human body, the difference in X-ray dose reaching the image detector is also large, and the contrast (density difference) on the captured image is also large.

  Further, since the bone part of the human body has a high Ca content with a high X-ray absorption rate, it is difficult to penetrate the human body and the X-ray dose reaching the image detector is reduced. Compared to the constituent element Si of asbestos, the X-ray absorption rate of Si is 1/3 of Ca, and it can be seen that the contrast between asbestos and alveoli is smaller than the contrast between bones and alveoli.

  In conventional X-ray images of the chest, the tone characteristics on the X-ray image are adjusted so that the bones, alveoli, and pulmonary blood vessels with large differences in X-ray absorption rates are easily read at the same time. is doing. However, under the gradation characteristics adjusted in this way, sufficient contrast cannot be obtained in an image portion having a relatively small difference in the reached X-ray dose, such as asbestos and alveoli, and the boundary portion between asbestos and alveoli It becomes impossible to distinguish.

  Therefore, in order to obtain an X-ray image in which minute asbestos can be visually recognized, the visibility of asbestos shadow can be improved by performing gradation conversion processing and / or frequency enhancement processing according to detection of asbestos shadow.

<Tone conversion processing>
The gradation conversion process is a process for adjusting density and contrast at the time of image output. When a doctor diagnoses the presence of a human body disease (for example, lung cancer in the chest) by interpretation of an X-ray image, the presence or absence of the disease is determined based on the density and contrast (gradation) of the structure on the X-ray image. The Therefore, by adjusting the density and contrast suitable for interpretation, a doctor's disease detection operation can be supported.

  The gradation conversion processing is performed in two stages, (1) normalization processing and (2) conversion processing using a basic LUT (lookup table), so that the desired signal value range and gradation characteristics are finally obtained. Tone conversion is performed.

  From the background that the screen / film method has been conventionally used for photographing, the doctor's interpretation ability (diagnosis) has been adopted even now that the digital processing method using the image detector 31 such as a volatile phosphor plate or FPD has been adopted. In order to maintain (performance), conversion processing of an input signal (read signal) is performed with a target of gradation characteristics (contrast) cultivated by the screen / film method.

  The gradation characteristic obtained by the screen / film system is an S-shaped curve as shown in FIG. In the gradation conversion process, an LUT indicating this gradation characteristic is prepared as a basic LUT, and after individual signal adjustment is performed on the target image by the normalization process, signal values are converted using the basic LUT. .

FIG. 8 shows the relationship between the X-ray dose detected by the image detector 31 (in the case of the phosphor plate) and the signal value of the X-ray image finally output according to the X-ray dose.
In the coordinate system of FIG. 8, the first quadrant shows the reading characteristic, and shows the relationship between the X-ray dose reaching the image detector 31 and the reading signal value (analog signal value). The second quadrant shows normalization characteristics, and shows the relationship between the read signal value and the normalized signal value (digital signal value) after the normalization process is performed. The third quadrant shows tone conversion characteristics and shows the relationship between the normalized signal value and the output density value (digital density signal value) converted by the basic LUT. Here, the output density value is a 12-bit resolution of 0 to 4095.

  In the second quadrant, the straight line indicating the normalization characteristic can adjust the output value range (size between SH and SL) by changing the slope thereof, and can also change the contrast of the entire image. This slope is defined as a G value. Further, by changing the intercept of the straight line indicating the gradation conversion characteristic, the height of the entire output value range (SH-SL movement) can be adjusted, and thereby the density of the entire image can be changed. Let this intercept be an S value.

  For example, comparing the case where normalization is performed with the straight line h2 and the straight line h3 shown in FIG. 8, by increasing the G value, the normalized signal value corresponding to asbestos corresponds to the linear region of the basic LUT. By improving the contrast, the visibility of the asbestos part is improved. At this time, the region where the transmitted X-ray dose is large is saturated, but there is no problem because there is no interpretation target in this portion.

  That is, the density range and contrast of the output image can be adjusted by controlling the gradient G value and intercept S value of the straight line indicating the gradation conversion characteristics as gradation conversion parameters.

The G value is determined by the following equation (4) for obtaining the gradient of the gradation characteristic curve in the screen / film system shown in FIG.
G = (J2-J1) / (logE2-logE1) (4)
here,
J1 = 0.25 + Fog, J2 = 2.0 + Fog, Fog = 0.2,
E1 and E2 are incident X-ray doses corresponding to J2 and J1, respectively.
In the case where each part of the human body such as the chest and breast is to be observed, the G value is generally about 2.5 to 5.0 in many cases.

Moreover, S value is calculated | required by following formula (5).
S = QR × K1 / K2 (5)
here,
QR is the quantization domain value,
K1 is the reached X-ray dose that results in a signal value 1535 (QR = 200, output density 1.2), and K2 is the actual reached X-ray dose of the pixel that has an output density of 1.2 in the image after gradation conversion.
The value of K1 is uniquely determined by the setting of the quantization region QR value before photographing.

The target image is normalized by performing signal conversion of the target image from a straight line determined by the obtained G value and S value. Then, gradation conversion is performed on the normalized image using the basic LUT to obtain a processed image having desired gradation characteristics.
That is, by performing normalization using the G value and the S value, gradation conversion can be performed in accordance with variations in X-ray dose and output characteristics of the output means even when the same LUT is used.

  The above is the content of the normal gradation conversion processing. In this embodiment, in order to improve the visibility of asbestos by focusing on the contrast difference between asbestos and alveoli in the output image, It is necessary to raise the G value regardless of the above equation (4) so that the contrast difference becomes large.

  In FIG. 8, the symbol h indicates a histogram of the X-ray dose for the lung field where asbestos is present. The signal value of the asbestos part is biased toward the low signal value side in the lung field part, and the signal width is narrow. Therefore, it is preferable that the density range (contrast) that can be output is not allocated to the signal width of the entire histogram, but is allocated to the narrow region so that the G value is 20 or more and the contrast of the asbestos image is improved.

<Frequency enhancement processing>
When gradation conversion is completed, frequency enhancement processing is performed on the processed image.
As a method of frequency enhancement processing, there are a method of performing non-sharp mask processing, a method of performing multi-resolution decomposition, and the like. Here, a method of performing multi-resolution decomposition described in JP-A-9-44645 and the like Will be described as an example.
In the method of performing multi-resolution decomposition, a processing target image is decomposed into a plurality of frequency band signals, and a signal in a desired frequency band is emphasized among the decomposed signals.

  First, every other pixel is sampled from the processing target image, and a pixel having a signal value “0” is interpolated between the sampled pixels. That is, “0” pixels are inserted every other row and every other row of the pixels arranged in a matrix in the sampled image.

  Next, the interpolated interpolated image is subjected to filter processing using a low-pass filter to obtain a low resolution image g1. This low resolution image g1 is obtained by extracting a low frequency band having a spatial frequency lower than half compared to the original image to be processed. This is because an image in a frequency band with a spatial frequency higher than half is lost by interpolating a pixel having a pixel value of “0” by sampling and a pixel value of “0”.

Then subtracted from the target image to low resolution image g _1, to obtain a high resolution image j _1. The high resolution image j ₁ are those spatial frequency image having high high frequency band than half are extracted, among the Nyquist frequency N of the original image is an image showing the frequency band of N / 2 to N.

Next, with respect to the low-resolution image g _1, filtering by the low-pass filter, it is subjected to interpolation processing to obtain a low-resolution image g _2, from the low-resolution image g ₁ by subtracting the low-resolution image g ₂ High-resolution images j ₂ is obtained. The high resolution image j ₂ Of the Nyquist frequency N of the original image, an image of the frequency band of N / 4 to N / 2 only.

By repeating the filtering process and the interpolation process in this way, a high resolution image j _k (k = 1, 2,...) Indicating the frequency band of N / 2 ^{k + 1 to} N / 2 ^k is ^obtained from the low resolution image gk. Obtainable.

When the high-resolution image j _k in the desired frequency band is obtained, the high-resolution image j _k in the frequency band to be emphasized is multiplied by the enhancement coefficient. Then, in order to restore the multi-resolution separated images, performing an inverse transformation of each image j _k containing high-resolution images the enhancement coefficient is multiplied.

First, subjected to interpolation processing between pixels with respect to the low resolution image g _k, and generates an inverse transformed image gg _k 4 times the size of the low resolution image g _k. Next, the inversely transformed image gg _k and the high resolution image j _k are added to obtain an added image gj _k−1 . An inversely transformed image gg _k-2 is generated by interpolation processing for this added image gj _k-1 , and a high resolution image j _k- 1 is added thereto to obtain an added image gj _k-2 .

Such processing is repeated, and an added image jk ₁ obtained by addition with the high resolution image j ₁ having the highest resolution is output as a processed image by frequency enhancement processing.

Here, the spatial frequency F (lp / mm) necessary for visually recognizing a structure having a width A (μm) or less must satisfy F ≧ 500 / A. In the magnified shooting, the subject width A on the image detector 31 is A = r × M + B obtained by multiplying the subject size r by the enlargement factor M and adding the blur width B. Asbestos with a diameter of 0.05 (μm) or more and 10 (μm) or less has a maximum size of 10 (μm), and therefore is represented by A = 10M + B. Therefore, the spatial frequency F necessary for visual recognition of asbestos is F = 500 / (10M + B).
Therefore, to enhance the visibility of asbestos in the output image, when performing the frequency emphasis performs enhancement processing for the spatial frequency F = 500 / (10M + B ) or higher-resolution images j _k.

  Here, the visual evaluation at the time of outputting to the film about the processed image which performed the said gradation conversion process and the frequency emphasis process is shown. The visual evaluation was performed on the output image output to the film after performing normal photographing and magnified photographing under the experimental conditions shown below, and performing image processing on the obtained photographed image under various processing conditions.

<Experimental conditions>
The subject was a glass wool having a diameter of 5 (μm) attached to a 5 cm thick acrylic plate and used as a simulated phantom of asbestos in the chest.
The X-ray tube used was a prototype manufactured by Konica Minolta, and the one having a focal diameter of D = 10 (μm). The company also used a prototype manufactured by the company.
The image detector used was a Regius plate RP-5PM and a Regius cassette RC-110M, which are phosphor plates manufactured by the same company.
The enlarged image read and generated detected by the image detector was read by Regius model 190 manufactured by Konica Minolta. The read pixel size is 43.75 (μm). On the other hand, the film output device used the company's DRYPRO model 793 to output to a film with a writing pixel size of 25 (μm). At this time, each pixel of the output target image and each pixel of the output image are associated with each other at a ratio of 1: 1 and output without performing interpolation processing.

<Shooting conditions>
The tube voltage of the X-ray tube at the time of imaging is 65 (kVp) and 80 (kVp), and the tube current is 1 (mA).
Further, the distance R3 from the focal point of the X-ray tube to the image detector is fixed at 3.5 (m), and the distances R1 and R2 are 2 ≧ R1 ≧ 0.07, 3.43 ≧ R2 ≧ 1.5, respectively. Shooting was performed in a range in which the magnification rate M was 1 ≦ M ≦ 50.
Table 2 below shows the photographing conditions at this time and the measurement result of the blur B caused by the conditions. In order to identify the shooting conditions individually for each shooting condition, the shooting condition No. Is granted.

<Image processing conditions>
A processed image obtained by performing gradation conversion processing and frequency enhancement processing on the phase contrast image obtained by photographing, and an enlarged image that has not been processed were created, and these were output by a film output device. For the processed image, the G value is changed in the gradation conversion process, and the frequency band (F) to be emphasized is changed in the frequency enhancement process.

<Evaluation criteria>
The evaluation criteria for the enlarged image output and formed on the film are as follows.
◎: Each of the fibers can be clearly recognized ○: A group of several fibers can be recognized △: It can be seen that there is a lump of fibers ×: The fibers cannot be visually recognized In the above evaluation, The number of fibers that can be recognized is the same as that of the comparative example, but the sign of “+” is given when the appearance of the fibers is clearer.
In accordance with the above evaluation criteria, seven image evaluators observed the image on the film and evaluated the image of the glass wool fiber that was the subject.

  No. above. When shooting is performed under the shooting conditions of 1 to 9, and the obtained photographic image is subjected to gradation conversion processing alone, the gradation conversion processing with a fixed G value and the frequency enhancement processing are combined. The image evaluation results are shown in Table 3 below. Table 4 below shows the image evaluation results when both the gradation conversion processing and the frequency enhancement processing are performed.

  As shown in Table 3, it can be seen that by setting the G value to G> 20, the visibility is improved until the fibers can be finely identified. This may be due to the increase in contrast by adjusting the G value. Further, in the results 7 and 8 in which the enhancement processing is performed on the frequency band of 500 / (10M + B) or more, in particular, the imaging condition No. The best evaluation is obtained at 5 to 7, and it can be seen that the image quality clearly confirms the fibers.

From the results shown in Table 4, it can be seen that the image quality is such that the fibers can be visually recognized by performing the gradation conversion processing and the frequency enhancement processing together. Further, it is understood that each of the fibers can be clearly observed and the visibility is the best by emphasizing the frequency band of G> 20 and F = 500 / (10M + B) or more. .
In the above evaluation, only the case of the focal diameter D = 10 (μm) is shown, but when the same experiment was performed up to the focal diameter D = 30 (μm), the result was the focal diameter D = 10 ( The result was almost the same as in the case of μm).

<Tone reversal processing>
The gradation inversion process is one of image processes performed for asbestos detection, and is a process for inverting the density corresponding to the gradation level. For example, in the case of the minimum gradation 0 (display density: black) to the maximum gradation 1023 (display density: white), this is inverted and the display is displayed when the minimum gradation is 0, the display density is white, and the maximum gradation is 1023. Density: Assign to black.

  Asbestos is present in the lung field. Generally, the asbestos shadow has a low concentration (the transmitted X-ray dose reaching the image detector is small), but the background lung field is also a high concentration compared to the asbestos shadow, but the absolute value is in the low concentration range. As a whole, the contrast of the asbestos shadow becomes low. When the contrast is low, white and fine asbestos shadows are detected from the white lung field, which is very difficult to see. In order to increase the contrast of the asbestos shadow, it is possible to achieve a high contrast by the gradation conversion process, but the background lung field also has a high contrast, and as a result, the asbestos shadow becomes difficult to visually recognize.

  In this case, by performing the gradation inversion process as described above, the asbestos shadow has a high density, the lung field has a lower density than the asbestos shadow, and the black asbestos shadow is detected from the white lung field. Therefore, the image is easy to detect.

<Asbestos shadow candidate detection process>
In the detection process, an area showing a density change characteristic of asbestos shadow is detected as a candidate area for asbestos shadow from the processed image subjected to the gradation conversion process and / or the frequency enhancement process. In the processed image, a human body structure such as a lung field is crushed black (corresponding to the maximum density Dmax), and a bone portion is crushed white (corresponding to Dmin). Therefore, when asbestos is ingested, the background crushed black A pattern in which asbestos parts having a predetermined concentration are scattered in the parts. Such a pattern may be detected as an asbestos shadow.

Although any detection method can be applied, here, a method of detecting based on a concentration gradient as described in JP-A-10-91758 will be described.
First, a lung field region is extracted from the target image. As described in Japanese Patent Laid-Open No. 11-96380, extraction is performed by obtaining histograms in the main scanning direction and sub-scanning direction of the target image and comparing them with a matching histogram pattern. An area composed of pixel values that match a density area defined as a lung field area in the matching histogram pattern is extracted as a lung field area.

  Then, a vector concentration degree is calculated for each pixel in the lung field area, and an area composed of pixels in which the concentration degree exceeds a preset threshold is set as a primary candidate area. Next, a feature amount (average value of pixel values, area, maximum value of vector concentration, average value, etc.) is obtained for the primary candidate region, and false positive candidate regions in the primary candidate region are detected by discriminant analysis based on the feature amount. This is deleted from the primary candidate area. The region remaining after the deletion is output as the final asbestos shadow candidate region. In the discriminant analysis, a discriminating logic is created in advance using learning data as true-positive asbestos shadows and false-positive shadows. As the discrimination logic, any of Mahalanobis distance, neural network, etc. can be applied.

  The image processing unit 27 applies the above image processing to the entire image and the partial image while changing the processing conditions. The processing conditions include (1) G value of gradation conversion processing, (2) frequency band F value emphasized in frequency enhancement processing, and (3) presence / absence of gradation inversion processing.

These processing conditions are prepared for image processing for interpretation according to interpretation and for image processing for asbestos detection according to asbestos detection.
The image processing for image interpretation is image processing performed so as to obtain image characteristics suitable for image interpretation. The image processing for interpretation includes at least one of gradation conversion processing and frequency enhancement processing.
On the other hand, the image processing for asbestos detection is image processing performed so as to obtain an image characteristic that facilitates detection of asbestos shadows. The image processing for asbestos detection includes one or more of gradation conversion processing, frequency enhancement processing, and gradation inversion processing.

In the image processing for interpretation, (1) G value is about 2.5 to 4.0 (varies depending on the thickness of the subject W, etc.), (2) F ≧ 500 / A (in general, the detection target is 100 μm ≦ A ≦ 5 cm) ), (3) Invalid gradation inversion processing is set.
On the other hand, in the image processing for asbestos detection, processing conditions are set such that (1) G> 20, (2) F ≧ 500 / (10M + B), and (3) gradation inversion processing enabled.
Note that tone conversion processing, frequency enhancement processing, and tone inversion image processing may be performed individually, or a plurality of image processing may be performed by combining one or more of these image processing.

  As described above, the obtained processed image or the detection result of the asbestos shadow candidate is transmitted from the image processing apparatus 20 to the image server 40, and is stored in the image DB 40a in the image server 40.

  The film output device 30 forms an image on the film based on the input image and outputs the image.

The image server 40 includes an image DB 40a, and the image DB 40a stores a captured image (original image) obtained by the photographing apparatus 10, a processed image obtained by the image processing apparatus 20, and a detection result of asbestos shadows in a database. Save and manage its input and output.
For example, the image server 40 reads a medical image (original image, processed image) designated in response to a request from the display device 50 from the image DB 40 a and transmits the medical image to the display device 50.

  The image server 40 receives imaging order information from HIS (Hospital Information System) or RIS (Radiology Information System). The imaging order information refers to instruction information relating to examination imaging, and includes instruction information relating to a patient to be imaged, examination, and the like. The image server 40 associates the corresponding captured images and creates a database based on the imaging order information.

  The display device 50 is a terminal device used when a doctor interprets a captured image. As shown in FIG. 9, the display device 50 includes a control unit 51, an operation unit 52, a display unit 53, a storage unit 54, a communication unit 55, and the like.

  The control unit 51 includes a CPU, a RAM, and the like, and performs various calculations according to various control programs stored in the storage unit 54 or performs centralized control of each unit.

The operation unit 52 includes a mouse, a keyboard, and the like, generates an operation signal corresponding to these operations, and outputs the operation signal to the control unit 51.
The display unit 53 includes a display and displays various display screens according to the control of the control unit 51.

The storage unit 54 stores various control programs executed by the control unit 51, parameters necessary for the execution, data, and the like.
The communication unit 55 includes a communication interface and communicates with an external device on the network N.

Next, the operation of the medical image system 1 will be described with reference to FIG.
FIG. 10 is a flowchart for explaining the overall flow from photographing to displaying the photographed image in the medical image system 1.

  Since the imaging order information is transmitted from the HIS or the like to the image server 40 in advance, the imaging server 40 displays the imaging order information. The imaging engineer performs an imaging operation on the designated patient according to the imaging order information by an imaging method such as the designated imaging region.

In the photographing apparatus 10, photographing is performed according to the operation of the photographing engineer (step S1).
Shooting is performed by automatically switching between normal shooting and enlarged shooting under the control of the main body 33. This is because, as shown in FIG. 5A, the entire chest T of the subject is photographed by normal photographing, and parts P1 and P2 of the chest are magnified by magnified photographing. Here, shooting order information is issued in the following order and shooting contents, and a total of four shootings are performed accordingly.
(1) Normal shooting 1: Chest front, target position (0, 0)
(2) Normal shooting 2: Chest side, target position (0, 0)
(3) Enlarged shooting 1: Part P1, target position (x1, y1)
(4) Magnification shooting 2: part P2, target position (x2, y2)

  In the case of the normal imaging 1 of (1) above, as shown in FIG. 3, the image detector 31 is arranged immediately behind the subject, and normal imaging is performed using the X-ray source 21. Thereafter, when normal imaging 2 is performed, the X-ray source 21 is left as it is, and the subject is rotated 90 degrees to perform side imaging. Next, when performing magnified imaging 1, the X-ray source 21 is switched to the X-ray source 22 having a small focal diameter D2. Further, without changing the position of the subject, the arrangement positions of the X-ray source 22 and the image detector 31 are changed according to the designated magnification M, and the distances R1 and R2 are adjusted. Further, the target position is changed from (0, 0) to (x1, y1) by the movement of the X-ray source 22.

When performing magnified imaging 2, the target position of the X-ray source 22 is changed from (x1, y1) to (x2, y2), and the position of the image detector 31 is matched according to the changed position. The position of the image detector 31 is changed.
Note that a CR cassette is used as the image detector 31. When a cassette is used as the image detector 31, the cassette is exchanged every time shooting is performed.

  The image generation device 3 generates captured image data every time the above-described shooting (1) to (4) is performed, and each captured image of the whole image obtained by the normal shooting and the partial image obtained by the enlarged shooting is an image. It is transmitted to the server 40.

  In the image server 40, each captured image received from the imaging device 10 is stored in the image DB 40a. At this time, the shooting order information and each shot image are associated with each other, and each shot image is made into a database based on the corresponding shooting order information, and each shot image is stored in association with each other (step S2).

The association is performed by generating incidental information as shown in FIG. 11 for each captured image and writing it in the header area of the image.
As shown in FIG. 11, the incidental information includes a patient basic information table L1, an examination information table L2, a series information table L3, and an image detailed information table L4.

Patient information is stored in the patient basic information table L1. In addition, patient information LID given to distinguish individual patient information is written.
The inspection information table L2 stores inspection information related to the inspection for which imaging is requested. In addition, inspection information LID given to distinguish individual inspection information is written.

  In the series information table L3, series information regarding a series of captured images obtained in the same examination is stored. In the series information table L3, the position information of the target position is written as to whether the image is an entire image or a partial image. In the series information table L3, series information LID for distinguishing individual series information is given and stored.

  Detailed information about the image is written in the detailed image information table L4. In the case of a processed image subjected to image processing, its image processing type (image processing for interpretation or image processing for asbestos detection), processing conditions during image processing (G value, frequency F, conditions during gradation conversion processing) ) Is written. Further, the detailed image information table L4 stores detailed image information LID for individually distinguishing the detailed image information.

  Patient information, examination information, and series information are acquired from imaging order information. The detailed image information is acquired from the imaging device 10 for information related to image generation and from the image processing device 20 for information related to image processing.

  Since the whole image and the partial image are taken at the same time in one examination for the same patient, the patient basic information table L1 and the examination information table L2 have the same contents. That is, each captured image obtained by the same examination of the same patient can be associated with the patient information LID and the examination information LID.

Next, the associated whole image and the partial images P1 and P2 are transmitted from the image server 40 to the image processing apparatus 20 as an image to be processed.
In the image processing device 20, the entire image and the partial image are subjected to image processing, and asbestos shadow candidate detection processing is performed (step S3).

In the image processing apparatus 20, image processing for interpretation is performed on the entire image. The partial images of the portions P1 and P2 are subjected to two types of image processing for interpretation and asbestos detection. Thereafter, asbestos shadow candidate detection processing is performed using the partial image that has been subjected to asbestos detection image processing.
When the detection process ends, the detection result of the asbestos shadow candidate is transmitted to the image server 40 together with the processed image of the entire image and the partial image. In the image server 40, the processed images are associated with each other and stored in the image DB 40a. For the partial image, the detection result of the asbestos shadow candidate is attached as accompanying information.

The above is the flow from shooting to saving of a shot image.
Next, display of a stored captured image will be described.
In the display device 50, when a doctor designates an interpretation target patient via the operation unit 52, request information for requesting a captured image related to the patient designated by the control unit 51 is generated, and via the communication unit 55. To the image server 40.
In the image server 40, in response to the request information from the display device 50, the whole image and the processed image of the partial image related to the designated patient are searched in the image DB 40 a and transmitted to the display device 50.

  In the display device 50, the processed images of the whole image and the partial image acquired from the image server 40 are displayed in association with each other (step S4). Here, displaying in association means displaying the positional relationship between the entire image of the chest and a partial image thereof in association with each other.

  The entire image and the partial image can be displayed by switching the display contents according to an instruction operation from the operation unit 52. Hereinafter, the whole image that has undergone image processing for interpretation is the whole image for interpretation, the partial image that has undergone image processing for interpretation is an interpretation partial image, and the partial image that has undergone image processing for asbestos detection is a partial image that is detected That's it.

  First, as shown in FIG. 12, during the initial display, the entire interpretation image T1 and the interpretation partial images P11 and P21 are displayed side by side on the same screen as shown in FIG. At this time, the control unit 51 performs image processing necessary for display, such as trimming the entire image or the partial image. The interpretation whole image T1 is an image obtained by photographing the chest from the front, the interpretation partial image P11 is an image corresponding to the part P1, and the interpretation partial image P21 is an image corresponding to the part P2. Interpretation partial images P11 and P21 are enlarged as compared with the entire interpretation image T1, and the edge portion of the asbestos shadow becomes clearer due to the edge effect.

  In this interpretation screen, when an interpretation partial image P11 or P21 is selected and operated by a doctor, portions P1 and P2 corresponding to the selected interpretation partial image P11 or P12 in the overall interpretation image T1 by display control of the control unit 51. Is displayed. The doctor can identify the position of the partial image by this marker d1, and can easily grasp the positional relationship of the partial image with respect to the entire image.

  On the contrary, when the portions P1 and P2 corresponding to the interpretation partial images P11 and P21 are selected in the interpretation whole image T1, the edges of the interpretation partial images P11 and P21 corresponding to the selected portion P1 or P2 are selected. It may be configured to be identified and displayed by displaying a marker on the frame. In this case, the doctor can identify which partial image P11 or P12 is the partial image corresponding to the selected portion, and can easily grasp the partial image of the portion to be observed.

  In addition, when a doctor switches between interpretation and detection on the interpretation screen shown in FIG. 12, display control is performed by the control unit 51 in accordance with the switching operation, and the interpretation partial image P11 or P12 and the detection partial image are displayed. P12 or P22 is switched and displayed. The detected partial images P12 and P22 have an image quality (contrast and sharpness) in which the asbestos shadow is more emphasized than the interpretation partial images P11 and P21.

  Further, according to the selection operation of the whole interpretation image T1, the whole interpretation image T1 on the front is switched to the whole interpretation image T2 on the side as shown in FIG. 13 by the display control of the control unit 51. In addition, when there are other interpretation whole images taken from different photographing directions, in accordance with a batch display instruction, as shown in FIG. 14, the whole interpretation images T1 to T3 on the front and left and right sides are displayed on the same screen. Interpretation partial images P11 and P21 or detection partial images P12 and P22 may be displayed.

  The lung field has a part that overlaps with other organs such as the heart, and as for this overlapping part, the shadow of the organ overlaps the background, so it is difficult to detect asbestos shadows. In some cases, it is possible to observe the lung field where the duplication is eliminated.

  A detection result button d4 for instructing display of a detection result is displayed on each interpretation screen. When this detection result button d4 is operated, the detection result of the asbestos shadow candidate is displayed by display control of the control unit 51. Is displayed. At this time, the entire image and the partial image displayed on the interpretation screen are switched depending on whether or not an asbestos shadow candidate is detected. Specifically, when no asbestos shadow candidate is detected from any of the detected partial images P11 and P21, the switching display is not performed and the display state according to the operation of the doctor is maintained, but the asbestos shadow candidate Is detected, at least the detected partial image is always switched to the interpretation partial images P11 and P21.

For example, when the detection result button d4 is operated on the interpretation screen shown in FIG. 12, the detection result d2 is displayed on the interpretation screen as shown in FIG.
The detection result d2 is obtained by displaying a marker d3 indicating whether or not an asbestos shadow candidate is detected on the reduced image of the entire interpretation image T1. A marker d3 displayed with a solid line indicates that an asbestos shadow candidate is detected, and a marker d3 displayed with a dotted line indicates that an asbestos shadow candidate has been detected, but no candidate has been detected.

At this time, the interpretation partial image P11 is displayed for the portion P1 where the asbestos shadow candidate is detected, and the switching display is not performed for the portion P2 where the asbestos shadow candidate is not detected, and the interpretation portion displayed on the previous screen. One of the images P21 and P22 remains displayed.
After that, the interpretation partial image P11 can be switched to the detection partial image P12 by performing a switching operation.
In this way, the doctor first observes the interpretation partial image having an edge effect and then displays the detection partial image as necessary. The presence or absence of the onset of the species is confirmed, and when there is a suspicious shadow, it is possible to determine whether it is true positive or false positive based on the presence or absence of asbestos shadow in the detected partial image.

  In addition, the doctor can perform interpretation by referring to the detection result d2 of the asbestos shadow candidate. The detection result d2 is displayed on the same screen as the interpretation partial images P11 and P21 or the detection partial images P12 and P22. The interpretation partial images P11 and P21 have clear edges of the asbestos shadow due to the edge effect, and the detection partial images P12 and P22 further emphasize the asbestos shadow. Therefore, while comparing these images with the detection result d2, The presence or absence of asbestos can be diagnosed.

  As described above, according to the present embodiment, the imaging apparatus 10 performs switching between normal imaging and enlarged imaging in one inspection imaging, and obtains an entire image showing the entire chest and a partial image showing a part thereof. The image processing apparatus 20 performs image processing for interpretation on the entire image, and performs image processing for asbestos shadow detection and image interpretation on the partial image to generate processed images. Then, the display device 50 displays the processed image as a whole image, an image interpretation partial image, and a detection partial image in association with each other on the same screen.

  As a result, doctors can observe images that are magnified entirely or partially when visually detecting minute shadows such as asbestos shadows, and can easily and efficiently detect asbestos shadows. Can be done. In addition, a plurality of processed images subjected to image processing suitable for the purpose of interpretation can be combined for comparative observation.

  Further, it is possible to switch display between the interpretation partial image and the detection partial image, and the doctor can switch and display the image quality suitable for interpretation and the image quality suitable for asbestos shadow detection according to the purpose.

In addition, embodiment mentioned above is a suitable example to which this invention is applied, and is not limited to this.
For example, a configuration may be adopted in which an area to be reserved for shooting on the entire image T1 shown in FIG. 11 can be selected and operated so that a portion for performing enlarged shooting at the next inspection can be reserved when the entire image is displayed. In this case, the display device 50 generates instruction information for instructing that the selected portion is to be enlarged, and transmits the instruction information to the HIS or RIS that issues the imaging order information. In HIS and RIS, imaging order information is generated based on the instruction information and transmitted to the image server 40.

  When there is a part that the doctor wants to follow up, or when an asbestos shadow or a suspicious shadow is found during interpretation, the doctor can easily and specifically specify the part to be reserved for imaging from the whole image T1 being interpreted. Is efficient.

In addition, the normal photographing and the magnified photographing are performed in one inspection photographing, but first, the whole image is photographed by the normal photographing and displayed on the display device 50, and the portion where the magnified photographing is performed in the whole image. It is good also as a structure which can make a photography reservation.
In this configuration, only when the doctor wants to obtain a more detailed image by reading the entire image once and discovering the shadow of pneumoconiosis, mesothelioma, etc., or a suspicious shadow such as developing a disease. Since photographing is performed, the burden of photographing by the patient can be reduced. In addition, the doctor can easily make a reservation for taking a picture of the part that he / she wants to observe during the examination, which is efficient.

  In the above description, an example in which two whole images (front and side surfaces) and two partial images (parts P1 and P2) are photographed has been described. However, the number of images is not particularly limited. The two partial images were taken from the left lung field, but partial images may be taken from the left and right lung fields, and the part to be photographed is not particularly limited.

  In addition, the interpretation partial image, the detection partial image, and the like may be pasted as a schema on an electronic medical record or an electronic report. An interpretation partial image and a detection partial image can be used for reference at the time of diagnosis.

  Moreover, although the example which employ | adopted phase contrast imaging was demonstrated in this embodiment, you may employ | adopt a general expansion imaging method. In this case, the improvement in visibility due to the edge enhancement effect cannot be expected, but the visibility of asbestos shadows can be improved by employing the above-described image processing conditions and the display method of each processed image.

It is a figure which shows the system configuration | structure of the medical image system in this embodiment. It is a figure which shows the imaging device of FIG. It is a figure explaining normal imaging | photography and expansion imaging. It is a figure which shows the relationship between the edge intensity | strength in the edge effect of expansion imaging | photography, and a blur. It is a figure explaining the target at the time of normal imaging | photography and expansion imaging | photography. It is a figure which shows the internal structure of the image processing apparatus of FIG. It is a figure which shows the gradation characteristic made into the target. It is a figure which shows the flow of the conversion of the signal value at the time of a gradation conversion process. It is a figure which shows the internal structure of the display apparatus of FIG. It is a flowchart which shows the flow of the whole process in a medical image system. It is a figure which shows an example of the incidental information of a picked-up image. It is a figure which shows the example of an interpretation screen. It is a figure which shows the example of an interpretation screen. It is a figure which shows the example of an interpretation screen. It is a figure which shows the example of an interpretation screen.

Explanation of symbols

DESCRIPTION OF SYMBOLS 100 Medical image system 10 Imaging device 2 X-ray source 3 Image generation device 20 Image processing device 21a Control unit 27 Image processing unit 30 Film output device 40 Image server 50 Display device 51 Control unit 52 Operation unit 53 Display unit

Claims (7)

Photographing means for switching between normal photographing for photographing the entire chest of the subject and enlarged photographing for a part of the chest;
Data generating means for generating data of the whole image shot by the normal shooting and the partial image of the chest shot by the enlarged shooting;
First image processing means for performing first image processing including image processing for interpretation on the entire image;
Second image processing means for performing second image processing including image processing for image interpretation and image processing for asbestos shadow detection on the partial image;
Display means for performing image display;
Control means for associating and displaying the entire image subjected to the first image processing and the partial image subjected to the second image processing on the display means;
A medical image system comprising:   The medical image system according to claim 1, wherein the control unit displays the entire image subjected to the first image processing and the partial image subjected to the second image processing on the same screen. The image processing for image interpretation includes one or more of gradation conversion processing or frequency enhancement processing,
The medical image system according to claim 1, wherein the image processing for detecting asbestos shadow includes one or more of gradation conversion processing, frequency enhancement processing, and gradation inversion processing. Comprising an operation means for performing an instruction operation of display contents in the display means;
The control means switches between a partial image subjected to the image processing for interpretation and a partial image subjected to the image processing for asbestos detection in accordance with an instruction operation by the operation means. The medical image system according to any one of claims 1 to 3, wherein   The medical image system according to any one of claims 1 to 3, wherein the control unit identifies and displays a position corresponding to the partial image in the entire image displayed on the display unit. Comprising an operation means for performing an instruction operation of display contents in the display means;
6. The control unit according to claim 5, wherein when the partial image is selected and operated through the operation unit, a position corresponding to the selected partial image in the entire image is identified and displayed. Medical imaging system. Comprising an operation means for performing an instruction operation of display contents in the display means;
6. The control unit according to claim 5, wherein when the part corresponding to the partial image in the entire image is selected and operated through the operation unit, the partial image of the selected part is identified and displayed. The medical imaging system described.

Images