JP2013094229A - Data processing apparatus, medical equipment, data processing method and program - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a data processing apparatus capable of improving efficiency of radiologic interpretations without requiring radiologic interpretations per time phase by putting together the data of different time phases into a single piece of image data by compositing the data of color channels of each of the time phases acquired by a converting means.SOLUTION: The difference between image data of each of time phases (hepatic-arterial phase, portal-venous phase and hepatobiliary phase) after administering a contrast medium to a subject and image data before administration of the contrast medium to the subject is obtained. Then, the image data of the time phase after the differentiation corresponding to the hepatic-artery phase are converted into the data of a red channel, the image data of the time phase after the differentiation corresponding to the portal-venous phase are converted into the data of a blue channel, and the image data of the time phase after the differentiation corresponding to the hepatobiliary phase are converted into the data of a green channel. Then, the data of color channels of hepatic-arterial phase, portal-venous phase and hepatobiliary phase are composited to create RGB image data.

Description

  The present invention relates to a data processing apparatus for processing image data of an imaging region of the subject which a contrast agent is administered, medical device, data processing method, and a program.

  As a method of diagnosing a subject using a medical device such as a magnetic resonance apparatus, a CT device, or an ultrasonic diagnostic device, image data of each time phase that appears after a contrast agent is administered to the subject and the contrast agent is administered. How to get is known.

International Publication No. 2006/051831

  In recent years, in a multi-time phase contrast imaging, the number of images that must be the interpretation has very increased, the time required for image interpretation is longer. Therefore, it is desired to improve the interpretation efficiency.

A first aspect of the present embodiment is a data processing device that processes image data of an imaging region of a subject to which a contrast agent is administered,
Difference means for obtaining a difference between the image data of each time phase after administering the contrast agent to the subject and the image data before administering the contrast agent to the subject;
Conversion means for converting the image data of each time phase after the difference obtained by the difference means into data of different color channels for identifying each time phase;
Combining means for combining the data of the color channels of the respective time phases obtained by the converting means;
Is a data processing apparatus.
The second aspect of the present embodiment is a medical apparatus having the data processing apparatus of the first aspect.

A third aspect of the present embodiment is a data processing method for processing image data of an imaging region of a subject to which a contrast agent is administered,
A difference step for obtaining a difference between the image data of each time phase after administering the contrast agent to the subject and the image data before administering the contrast agent to the subject;
A conversion step of converting the image data of each time phase after the difference obtained by the difference step into data of different color channels for identifying each time phase;
A synthesizing step of synthesizing the data of the color channels of the respective time phases obtained by the converting step;
Is a data processing method.

A fourth aspect of the present embodiment is a program for processing image data of an imaging region of a subject to which a contrast agent is administered,
Difference processing for obtaining a difference between the image data of each time phase after administering the contrast agent to the subject and the image data before administering the contrast agent to the subject;
Conversion processing for converting the image data of each time phase after the difference obtained by the difference processing into data of different color channels for identifying each time phase;
A combining process for combining the data of the color channels of the respective time phases obtained by the conversion process;
Is a program for causing a computer to execute.

  By synthesizing the color channel data of each time phase obtained by the conversion means, the data of different time phases can be made into one image data, so there is no need to interpret each time phase, Efficiency can be improved.

1 is a schematic view of a magnetic resonance apparatus according to a first embodiment of the present invention. It is a figure which shows the scan performed with this form. It is a figure which shows an imaging | photography site | part schematically. 3 is a diagram showing an operation flow of the MR apparatus 100. FIG. It is explanatory drawing of the method of calculating | requiring the difference of image data. Image data ΔD ₁ ~ΔD ₃ of each phase after the difference is an explanatory view when converting the data of the color channels to identify each time phase. It is explanatory drawing of the production method of RGB image data _Drgb . It is an example of the tomographic plane displayed on the monitor. FIG. 10 is an explanatory diagram of a scan executed in a second form.

  Hereinafter, although the form for inventing is demonstrated, this invention is not limited to the following forms.

(1) First Embodiment FIG. 1 is a schematic view of a magnetic resonance apparatus according to a first embodiment of the present invention.
A magnetic resonance apparatus (hereinafter referred to as “MR apparatus”, MR: Magnetic Resonance) 100 includes a magnet 2, a table 3, a receiving coil 4, and the like.

  The magnet 2 has a bore 21 in which the subject 12 is accommodated. The magnet 2 includes a superconducting coil 22, a gradient coil 23, a transmission coil 24, and the like. The superconducting coil 22 applies a static magnetic field, the gradient coil 23 applies a gradient pulse, and the transmission coil 24 transmits an RF pulse. In place of the superconducting coil 22, a permanent magnet may be used.

  The table 3 has a cradle 3a. The cradle 3a is configured to be able to move into the bore 21. The subject 12 is transported to the bore 21 by the cradle 3a.

  The reception coil 4 is attached to the abdomen of the subject 12. The receiving coil 4 receives a magnetic resonance signal from the subject 12.

  The MR apparatus 100 further includes a sequencer 5, a transmitter 6, a gradient magnetic field power supply 7, a receiver 8, a central processing unit 9, an operation unit 10, and a display unit 11.

  Under the control of the central processing unit 9, the sequencer 5 sends pulse sequence information to the transmitter 6 and the gradient magnetic field power supply 7.

  The transmitter 6 outputs a signal for driving the RF coil 24 based on the information sent from the sequencer 5.

  The gradient magnetic field power supply 7 outputs a signal for driving the gradient coil 23 based on the information sent from the sequencer 5.

  The receiver 8 processes the magnetic resonance signal received by the receiving coil 4 and outputs it to the central processing unit 9.

  The central processing unit 9 implements various operations of the MR apparatus 100 such as transmitting necessary information to the sequencer 5 and the display unit 11 and reconstructing an image based on data received from the receiver 8. The operation of each part of the MR apparatus 100 is controlled. The central processing unit 9 is constituted by a computer, for example. The central processing unit 9 includes image data creation means 91 to composition means 94 and the like.

  The image data creation unit 91 creates image data of each time phase after the contrast medium is administered to the subject 12 and image data before the contrast medium is administered to the subject 12.

  The difference means 92 obtains a difference between the image data of each time phase after the contrast medium is administered to the subject 12 and the image data before the contrast medium is administered to the subject 12.

  Converting means 93, the image data for each time phase after the resulting difference by the difference unit 92, into data of a different color channels for identifying each time phase.

  The synthesizing unit 94 synthesizes the color channel data of each time phase obtained by the converting unit 93.

  The central processing unit 9 is an example of an apparatus constituting the image data generating unit 91 to combining means 94, by executing a predetermined program, functions as these means. The central processing unit is an example of a data processing device.

The operation unit 10 is operated by an operator and inputs various information to the central processing unit 9. The display unit 11 displays various information.
The MR apparatus 100 is configured as described above.

FIG. 2 is a diagram showing a scan executed in this embodiment, and FIG. 3 is a diagram schematically showing an imaging region.
In this embodiment, scans SC _{1 to} SC ₄ are executed with the region including the liver as the imaging region R.

The scan SC ₁ is a scan for imaging the imaging region R before the contrast medium is administered to the subject 12. The scans SC _{2 to} SC ₄ are scans for imaging the imaging region R after the contrast medium is administered to the subject 12.

Scan SC ₂ is imaging region R is performed when the hepatic arterial phase. The hepatic artery phase is a time phase when the contrast medium is mainly taken into the liver from the hepatic artery, and at an early stage after the contrast medium is administered (for example, several tens of seconds after the contrast medium is administered) It is a time phase that appears.

Scan SC ₃ is imaging region R is performed when the portal phase. The portal vein phase is a time phase when the contrast medium is mainly taken into the liver from the portal vein, and is a time phase that appears after the hepatic artery phase (for example, several tens of seconds after the hepatic artery phase).

Scan SC ₄ is imaging region R is performed when the hepatocyte imaging phase. The hepatocyte contrast phase is a time phase suitable for acquiring a normal hepatocyte portion with a high signal, and a stage after a certain amount of time has passed since the contrast medium was administered (for example, the contrast medium was administered). It is a time phase that appears several minutes later.
Next, an operation flow of the MR apparatus 100 will be described.

FIG. 4 is a diagram showing an operation flow of the MR apparatus 100.
In step ST1, perform a scan SC ₁ before administering a contrast agent into the subject 12. By performing a scan SC _1, a magnetic resonance signal from the imaging region R before the administration of a contrast agent into the subject 12 is acquired. Image data generating means 91 (see FIG. 1), based on the magnetic resonance signals obtained by scanning SC _1, to create the image data of the imaging region R before administering the contrast medium. After running the scan SC _1, the process proceeds to step ST2.
In step ST2, a contrast medium is administered to the subject 12.

At step ST3, the performing the scan SC ₂ for imaging sites R collects magnetic resonance signal when the hepatic arterial phase. An example of a method for determining whether or not the imaging region R is in the hepatic artery phase is to collect a magnetic resonance signal from the hepatic artery (or a blood vessel upstream of the hepatic artery) before administering the contrast agent. There is a method in which scanning is repeatedly executed to obtain a temporal change in signal intensity. When the bolus of the contrast agent approaches the hepatic artery (or the blood vessel upstream of the hepatic artery), the signal intensity increases accordingly. Therefore, by obtaining the temporal change in the signal intensity, the imaging site is the hepatic artery phase. It can be determined whether or not. Image data generating means 91, based on the magnetic resonance signals obtained by scanning SC _2, to create the image data of the imaging region R in hepatic arterial phase. When you have finished the scan SC _2, the process proceeds to step ST4.

In step ST4, perform a scan SC ₃ for imaging sites R collects magnetic resonance signals when the portal phase. As an example of a method for determining whether or not the imaging region R is in the portal vein phase, a scan for collecting a magnetic resonance signal from the portal vein (or a blood vessel upstream of the portal vein) is repeatedly executed, and the signal intensity There is a method to calculate the time change of Image data generating means 91, based on the magnetic resonance signals obtained by scanning SC _3, to create the image data of the imaging region R in portal phase. When the scan SC ₃ is completed, the process proceeds to step ST5.

In step ST5, perform a scan SC ₄ for imaging sites to collect magnetic resonance signals when hepatocyte imaging phase. The hepatocyte contrast phase appears at a stage where a certain amount of time has elapsed since the contrast medium was administered (for example, several tens of minutes after the contrast medium was administered). Therefore, the operator executes the scan SC ₄ when several tens of minutes (for example, 20 minutes) have elapsed since the contrast medium was administered. Image data generating means 91, based on the magnetic resonance signals obtained by scanning SC _4, to create the image data of the imaging region R in hepatocytes imaging phase. When the scan SC ₄ is completed, the process proceeds to step ST6.

  In step ST6, the difference means 92 (refer FIG. 1) calculates | requires the difference of the image data of each time phase after administering a contrast agent, and the image data before administering a contrast agent.

FIG. 5 is an explanatory diagram of a method for obtaining a difference between image data.
FIG. 5A is an explanatory diagram for obtaining the difference between the image data of the hepatic artery phase and the image data before administration of the contrast agent, and FIG. 5B is the image data of the portal vein phase and the contrast agent administration. FIG. 5C is an explanatory diagram for obtaining the difference between the previous image data and FIG. 5C is an explanatory diagram for obtaining the difference between the image data of the hepatocyte contrast phase and the image data before administration of the contrast agent.

For example, when the difference between the image data of the hepatic artery phase and the image data before administration of the contrast agent is obtained (see FIG. 5A), the difference in signal intensity is obtained for each voxel. For example, the voxel V _i when obtaining the difference between the signal strength at, from the signal strength S _i1 of the voxel V _i of the image data D ₁ of the hepatic artery phase, the signal strength of the voxel V _i of the image data D ₀ before contrast administration S _i0 is subtracted to determine the difference ΔS _i1 in the signal intensity of the voxel Vi. For other voxels, the difference in signal strength is obtained in the same procedure. In this way, image data ΔD ₁ of the hepatic artery phase after the difference is obtained.

Similarly, the image data D ₂ of the portal vein, the image data D ₀ before contrast administration subtracted to obtain the image data [Delta] D ₂ of portal phase after difference (see FIG. 5 (b)), further Then, the image data D ₀ before contrast medium administration is subtracted from the image data D ₃ of the hepatocyte contrast phase to obtain the image data ΔD ₃ of the hepatocyte contrast phase after the difference (see FIG. 5C). After obtaining the image data ΔD _{1 to} ΔD ₃ of each time phase after the difference, the process proceeds to step ST7.

In step ST7, the conversion means 93 (see FIG. 1) converts the image data ΔD _{1 to} ΔD ₃ of each time phase after the difference obtained in step ST6 into color channel data for identifying each time phase. To do.

FIG. 6 is an explanatory diagram when the image data ΔD _{1 to} ΔD ₃ of each time phase after the difference is converted into data of color channels for identifying each time phase.

In this embodiment, the difference hepatic artery phase image data ΔD ₁ is converted into red channel data (see FIG. 6A), and the difference portal phase image data ΔD ₂ is converted into blue channel data. with (see FIG. 6 (b)), the image data [Delta] D ₃ hepatocyte imaging phase after differential converting the green channel of the data (see Figure 6 (c)).

For example, when the image data ΔD ₁ of the hepatic artery phase after the difference is converted into red channel data (see FIG. 6A), the gradation value of the red channel is determined based on the difference in signal intensity of each voxel. To do. In this embodiment, the gradation is divided into 256 gradations (minimum value 0, maximum value 255), but is not limited to 256 gradations, and may be, for example, 128 gradations. The FIG. 6 (a), the basis on the basis of the difference [Delta] S _i1 of the signal intensity of a voxel _{V i,} and an example of when determining the gradation value _{G ri} of the red channel, the difference [Delta] S _j1 signal intensity of a voxel _{V j} An example in which the gradation value G _rj of the red channel is determined is shown. Incidentally, the difference [Delta] S _i1 of the signal intensity of a voxel _{V i,} between the difference [Delta] S _j1 signal intensity of a voxel _{V j} is the following relationship.
ΔS _i1 > ΔS _j1 (1)

Since the signal intensity difference of the voxel V _i is ΔS _i1 , the conversion unit 93 obtains the gradation value G _ri corresponding to the value of ΔS _i1 from the gradation values 0 to 255 that the red channel can take. Therefore, the voxel V _i of the image data ΔD ₁ of the hepatic artery phase after the difference is converted into a red channel having the gradation value G _ri . On the other hand, the difference [Delta] S _j1 signal intensity of a voxel _{V j} is smaller than the difference [Delta] S _i1 of the signal intensity of a voxel _{V i,} the voxel _{V j} is the red channel of smaller grayscale value _{G rj} than voxel _{V i} conversion Is done.

Similarly, for other voxels, the gradation value of the red channel is determined based on the signal intensity difference. In this manner, hepatic artery phase red channel data Dr can be obtained from the difference hepatic artery phase image data ΔD ₁ .

The portal phase image data ΔD ₂ after the difference is converted into blue channel data Db (see FIG. 6B), and the hepatocyte contrast phase image data ΔD ₃ is converted into green channel data Dg. (See FIG. 6 (c)). The method for determining the gradation value of the blue channel and the green channel is the same as the method of determining the gradation value of the red channel.

In this way, the image data ΔD ₁ of the hepatic artery phase after the difference, the image data ΔD ₂ of the portal vein phase after the difference, and the image data ΔD ₃ of the hepatocyte contrast phase after the difference are the data D of the red channel, respectively. _r (hepatic artery phase data), blue channel data D _b (portal vein phase data), and green channel data D _g (hepatocyte contrast phase data). When this conversion ends, the process proceeds to step ST8.

In step ST8, the combining means 94 (see FIG. 1) performs red channel data D _r (hepatic artery phase data), blue channel data D _b (portal phase data), and green channel data D _g (liver phase data). Cell contrast phase data) is synthesized to create RGB image data (see FIG. 7).

FIG. 7 is an explanatory diagram of a method of creating the RGB image data D _rgb .
When creating RGB image data, red channel data D _r (hepatic artery phase data), blue channel data D _b (portal vein phase data), green channel data D _g (hepatocyte contrast phase data) For each voxel. For example, to create a data of the voxel V _i of the RGB image data, synthesizing the data of the following voxel.
(1) the gradation value _{G ri} of the voxel _{V i} of the data _{D r} in the red channel
(2) _Tone value G _bi of voxel V _i of blue channel data D _b
(3) _Tone value G _gi of voxel V _i of green channel data D _g

The gradation values G _ri , G _bi , and G _gi correspond to the gradation value of the red channel corresponding to the hepatic artery phase, the gradation value of the blue channel corresponding to the portal vein phase, and the hepatocyte contrast phase, respectively. It represents the gradation value of the green channel. Therefore, the RGB data DV _i = (G _ri , G _bi , G _gi ) in the voxel V _i is obtained by synthesizing these tone values G _ri , G _bi , and G _gi . Similarly, for other voxels, red channel data D _r (hepatic artery phase data), blue channel data D _b (portal vein phase data), green channel data D _g (hepatocyte contrast phase data). Data). In this way, RGB image data D _rgb of the imaging region is created. When the RGB image data D _rgb is created, the process proceeds to step ST9.

In step ST9, the interpretation doctor interprets the RGB image data D _rgb . Radiologist, in order to perform the interpretation of the RGB image data _{D rgb,} it displays the RGB image data _{D rgb} monitor. In this embodiment, when displaying the RGB image data _{D rgb,} to display the tomographic plane of the RGB image data _{D rgb} (see FIG. 8).

FIG. 8 is an example of a tomographic plane displayed on the monitor. In Figure 8, an example of displaying the image data X axial planes SA across the voxel _{V i} of the RGB image data _{D rgb} is shown.

Each pixel of the image data X of the axial plane SA is represented by RGB data. For example, the RGB data DP _i of the pixel P _i (the pixel corresponding to the voxel V _i ) has a red channel gradation value G _ri corresponding to the hepatic artery phase and a blue channel gradation value G _bi corresponding to the portal vein phase. , And the tone value G _gi of the green channel corresponding to the hepatocyte contrast phase. Other pixels of the image data X, similar to the pixel P _i, is represented by RGB data.

  Each pixel of the image data X of the axial surface SA displayed on the monitor corresponds to the gradation value of the red channel corresponding to the hepatic artery phase, the gradation value of the blue channel corresponding to the portal vein phase, and the hepatocyte contrast phase. It is represented by the gradation value of the green channel. Therefore, the interpretation doctor simply looks at the image data X of the axial surface SA displayed on the monitor, and in any time phase among the three time phases (hepatic artery phase, portal vein phase, and hepatocyte contrast phase). It can be confirmed which part of the surface SA is stained with the contrast agent. For this reason, the interpretation doctor can perform interpretation without looking at the image data of each of the three time phases, so that the time required for interpretation can be shortened and the interpretation efficiency can be improved. In particular, regarding liver tumor evaluation with contrast agents using Gd-EOB-DTPA (ethoxybenzyl diethylenetriamine pentaacetic acid), it is necessary to evaluate the slight contrast of the hepatic arteries. By converting into data of different color channels, it becomes easy to identify the degree of contrast medium staining.

  In this embodiment, the red channel, the blue channel, and the green channel are allocated to the hepatic artery phase, the portal vein phase, and the hepatocyte contrast phase, respectively, but the allocation of the color channel is limited to this. There is nothing. For example, a blue channel may be assigned to the hepatic artery phase and a red channel may be assigned to the portal phase. However, in the medical field, arteries are usually displayed in red and veins are displayed in blue. Accordingly, in this embodiment, a red channel is assigned to the time phase related to the artery (hepatic artery phase). The blue channel is assigned to the time phase (portal vein phase) related to veins. Therefore, the interpreting physician can intuitively recognize the portion stained with the contrast agent in the hepatic artery phase and the portion stained with the contrast agent in the portal vein phase by identifying the color of the image displayed on the monitor. it can.

In this embodiment, image data of three time phases of the hepatic artery phase, the portal vein phase, and the hepatocyte contrast phase is acquired, but it is not always necessary to acquire image data of the three time phases. Only one time phase of image data may be acquired. For example, only image data of two time phases of the hepatic artery phase and the hepatocyte contrast phase may be acquired. In this case, the portal phase image data is not acquired. Therefore, when creating RGB image data, the gradation value of the blue channel corresponding to the portal phase is set to zero, and the red channel data corresponding to the hepatic artery phase is set. and D _r, may be synthesized and data D _g of the green channel corresponding to the hepatocyte imaging phase. However, since the gradation value of the blue channel is set to zero, the created RGB image data does not use the blue channel, and is image data created using only the red channel and the green channel. .

(2) Second Embodiment In the second embodiment, a case where the blood flow of the leg of the subject 12 is imaged will be described.

FIG. 9 is an explanatory diagram of a scan executed in the second mode.
In the second mode, scans SC _{1 to} SC ₄ are executed.

Scan SC ₁ is a scan that is performed prior to administering the contrast medium.
Scan SC ₂ is a scanning bolus of contrast agent is performed in a first time phase when it reaches to the position p of the leg.
Scan SC ₃ is a scanning bolus of contrast agent is performed in a second time phase when it reaches to the position q of the leg.
Scan SC ₄ is a scanning bolus of contrast agent is performed in the third time phase when it reaches to the position r of the leg.

  Next, a procedure for creating RGB image data in the second embodiment will be described. This description will be made with reference to the flow of FIG. 4 as in the first embodiment.

In step ST1, it performs a scan SC _1, and acquires the image data before the contrast agent is administered. Next, a contrast medium is administered in step ST2. In steps ST3, ST4, and ST5, scans SC ₂ , SC ₃ , and SC ₄ are executed, respectively. By performing the scans SC ₂ , SC ₃ , and SC ₄ , image data of the legs in the first time phase, the second time phase, and the third time phase after the contrast agent is administered are obtained. It is done. When the scans SC ₂ , SC ₃ , and SC ₄ are executed, the process proceeds to step ST6.

  In step ST6, the signal intensity obtained by the first time phase, the second time phase, and the third time phase and the signal intensity obtained before administration of the contrast agent in the same procedure as in the first embodiment. And the image data of each time phase after the difference is calculated (see FIG. 5).

  In step ST7, the image data of each time phase after the difference is converted into red channel data, blue channel data, and green channel data in the same procedure as in the first embodiment (see FIG. 6).

  In step ST8, the red channel data, the blue channel data, and the green channel data corresponding to each time phase are synthesized by the same procedure as in the first embodiment to create RGB image data (see FIG. 7). . Finally, in step ST9, RGB image data is displayed on the monitor and interpretation is performed.

  In the second embodiment, by synthesizing the image data of the blood flow in the legs obtained for each time phase, we are creating an RGB image data. Therefore, the image interpretation doctor can determine how fast the blood flowing through the leg is by identifying the color of the tomographic image displayed on the monitor.

  In the second embodiment, RGB image data is generated by acquiring three time phase data, but RGB image data may be generated by acquiring two time phase data.

  In the first and second embodiments, the case where the MR device acquires image data of each time phase after contrast medium administration and synthesizes the RGB image data has been described. However, the present invention is limited to the MR device. not Rukoto may use a medical device such as a CT apparatus acquires image data for each time phase after contrast administration, it applied to the case of synthesizing the RGB image data.

  In the first and second embodiments, examples of creating RGB image data have been described, but the present invention is not limited to creating RGB image data. For example, cyan (C), yellow (Y), magenta (M), it may be created image data using black (K). In this case, it is possible to synthesize four time phase data into one image data.

2 Magnet 3 Table 3a Cradle 4 Receiving coil 5 Sequencer 6 Transmitter 7 Gradient magnetic field power supply 8 Receiver 9 Central processing unit 10 Operation unit 11 Display unit 12 Subject 21 Bore 22 Superconducting coil 23 Gradient coil 24 Transmitting coil 91 Image data creation Means 92 Difference means 93 Conversion means 94 Composition means

Claims (15)

A data processing device that processes image data of an imaging region of a subject to which a contrast agent is administered,
Difference means for obtaining a difference between the image data of each time phase after administering the contrast agent to the subject and the image data before administering the contrast agent to the subject;
Conversion means for converting the image data of each time phase after the difference obtained by the difference means into data of different color channels for identifying each time phase;
Combining means for combining the data of the color channels of the respective time phases obtained by the converting means;
A data processing apparatus. The synthesis means includes
The data processing apparatus according to claim 1, wherein the color channel data of each time phase obtained by the conversion unit is synthesized to generate color image data.   The data according to claim 2, further comprising image data creation means for creating image data at each time phase after the contrast medium is administered to the subject and image data before the contrast medium is administered to the subject. Processing equipment. The image data creation means includes
The first time phase image data, the second time phase image data, and the third time phase image data are created as the image data of each time phase after the contrast medium is administered to the subject. The data processing apparatus according to claim 3. The difference means is
Obtaining a difference between the image data of the first time phase, the image data of the second time phase, and the image data of the third time phase, and the image data before administering the contrast agent to the subject;
The converting means includes
The image data of the first time phase after the difference is converted into the data of the first color channel, the image data of the second time phase after the difference is converted into the data of the second color channel, and the first data after the difference is converted. 3 time phase image data is converted into data of the third color channel,
The synthesis means includes
The data processing apparatus according to claim 4, wherein the color image data is created by combining the data of the first color channel, the data of the second color channel, and the data of the third color channel.   The data of the first color channel, the data of the second color channel, and the data of the third color channel are data of a red channel, data of a blue channel, and data of a green channel, respectively. 5. The data processing device according to 5. The imaging region includes the liver,
The first time phase, the second time phase, and the third time phase are a hepatic artery phase, a portal vein phase, and a hepatocyte contrast phase, respectively. The data processing apparatus described in 1. The image data creation means includes
The data processing device according to claim 3, wherein the first time phase image data and the second time phase image data are created as image data of each time phase after the contrast medium is administered to the subject. . The difference means is
Obtaining a difference between the image data of the first time phase and the image data of the second time phase and the image data before administering the contrast agent to the subject;
The converting means includes
Converting the image data of the first time phase after the difference into the data of the first color channel, converting the image data of the second time phase after the difference into the data of the second color channel,
The synthesis means includes
The data processing apparatus according to claim 8, wherein the color image data is generated by combining the data of the first color channel and the data of the second color channel. The color image data is
The data processing apparatus according to claim 9, wherein the data processing apparatus is image data created using any two color channels of a red channel, a blue channel, and a green channel. The imaging region includes the liver,
The data processing device according to any one of claims 8 to 10, wherein the first time phase and the second time phase are a hepatic artery phase and a hepatocyte contrast phase, respectively.   The data processing apparatus according to claim 1, wherein the imaging part includes a leg portion.   A medical device comprising the data processing device according to any one of claims 1 to 12. A data processing method for processing image data of an imaging region of a subject to which a contrast agent is administered,
A difference step for obtaining a difference between the image data of each time phase after administering the contrast agent to the subject and the image data before administering the contrast agent to the subject;
A conversion step of converting the image data of each time phase after the difference obtained by the difference step into data of different color channels for identifying each time phase;
A synthesizing step of synthesizing the data of the color channels of the respective time phases obtained by the converting step;
A data processing method. A program for processing image data of an imaging region of a subject to which a contrast agent is administered,
Difference processing for obtaining a difference between the image data of each time phase after administering the contrast agent to the subject and the image data before administering the contrast agent to the subject;
Conversion processing for converting the image data of each time phase after the difference obtained by the difference processing into data of different color channels for identifying each time phase;
A combining process for combining the data of the color channels of the respective time phases obtained by the conversion process;
A program to make a computer execute.