IMAGE PROCESSING APPARATUS, IMAGE PROCESSING METHOD, AND IMAGE PROCESSING PROGRAM

An image processing apparatus that acquires a plurality of radiographic images captured by irradiating a photographic subject with radiations at different tube voltages. From the plurality of radiographic images, the image processing apparatus generates, for a region of interest selected in the radiographic image, a first region image equivalent to an image to be obtained when a radiation at a first virtual tube voltage is radiated. From the plurality of radiographic images, the image processing apparatus generates, for an unselected region other than the region of interest in the radiographic image, a second region image equivalent to an image to be obtained when a radiation at a second virtual tube voltage according to a distance from the region of interest is radiated. The image processing apparatus generates a combined image obtained by combining the first region image and the second region image together.

BACKGROUND

Technical Field

The present disclosure relates to an image processing apparatus, an image processing method, and an image processing program.

Related Art

In the related art, a radiographic image is captured with an imaging apparatus such as a computed tomography (CT) apparatus. As techniques related to capturing of such a radiographic image, techniques for generating a combined image obtained by combining a plurality of radiographic images captured by irradiating a photographic subject with radiations at different tube voltages are known (see JP6261915B and JP2011-172803A).

SUMMARY

With the techniques for combining a plurality of radiographic images captured by irradiating a photographic subject with radiations at different tube voltages, a combined image can be used as a radiographic image that would be obtained if a radiation at any virtual tube voltage were radiated. Specifically, for example, by combining a first radiographic image captured by irradiating a photographic subject with a radiation at a tube voltage of 80 kVp and a second radiographic image captured by irradiating the photographic subject with a radiation at a tube voltage of 140 kVp together, a combined image below can be generated. That is, in this case, a combined image equivalent to an image to be obtained when a radiation at any virtual tube voltage is radiated, such as a radiographic image equivalent to an image to be obtained when a radiation at 40 keV is radiated or a radiographic image equivalent to an image to be obtained when a radiation at 100 keV is radiated, can be generated. Note that in these examples, the tube voltage in unit “kVp” represents a voltage of a peak of consecutive spectra at the time of actual image capturing, and the tube voltage in unit “keV” represents a voltage of a single spectrum at the time of generation of a combined image.

Thus, for example, by selecting a region of interest in a radiographic image and setting pixel values of the selected region of interest as pixel values in the case of a relatively low tube voltage, a contrast effect of the region of interest can be emphasized. In addition, by setting the pixel values of the selected region of interest as pixel values in the case of a relatively high tube voltage, noise in the region of interest can be reduced.

However, the techniques described in JP6261915B and JP2011-172803A do not take into account which tube voltage the pixel values in a region (hereinafter, referred to as an “unselected region”) other than the selected region of interest correspond to.

For example, when only the pixel values of the selected region of interest is set as pixel values corresponding to a designated tube voltage, a structure such as an organ that is present in the unselected region is not displayed as illustrated inFIG.1as an example. Thus, a positional relationship between the region of interest and the structure that is present in the unselected region is unknown.FIG.1illustrates an example in which a blood vessel region is selected.

In contrast, pixel values of the unselected region are conceivably set as pixel values corresponding to a default tube voltage. In this case, as illustrated inFIG.2as an example, since the tube voltage abruptly changes between the region of interest and the unselected region, the pixel values also abruptly change. Consequently, an unnatural change in the pixel values occurs.FIG.2illustrates an example in which a partial region of the kidney is selected.

The present disclosure is made in view of the circumstances described above, and an object thereof is to provide an image processing apparatus, an image processing method, and an image processing program capable of suppressing an unnatural change in pixel values in a radiographic image.

An image processing apparatus according to the present disclosure is an image processing apparatus that generates, using a plurality of radiographic images captured by irradiating a photographic subject with radiations at different tube voltages, a combined image that is equivalent to an image to be obtained when a virtual tube voltage is radiated. The image processing apparatus includes at least one processor. The at least one processor is configured to acquire a plurality of radiographic images captured by irradiating a photographic subject with radiations at different tube voltages; acquire information representing at least one region of interest selected in a radiographic image among the plurality of radiographic images and a first virtual tube voltage for the region of interest; derive, for an unselected region other than the region of interest in the radiographic image, a second virtual tube voltage according to a distance from the region of interest; generate, for the region of interest, a first region image from the plurality of radiographic images, the first region image being equivalent to an image to be obtained when a radiation at the first virtual tube voltage is radiated; generate, for the unselected region, a second region image from the plurality of radiographic images, the second region image being equivalent to an image to be obtained when a radiation at the second virtual tube voltage is radiated; and generate a combined image obtained by combining the first region image and the second region image together.

In the image processing apparatus according to the present disclosure, the at least one processor may be configured to derive the second virtual tube voltage according to the distance from the region of interest, using a function that outputs a tube voltage value that increases as the distance from the region of interest increases.

In the image processing apparatus according to the present disclosure, the at least one processor may be configured to, in a case of acquiring information representing a plurality of the regions of interest, derive, for the unselected region, the second virtual tube voltage according to a distance from a closest region of interest among the plurality of regions of interest.

An image processing method according to the present disclosure is an image processing method to be executed by a processor included in an image processing apparatus that generates, using a plurality of radiographic images captured by irradiating a photographic subject with radiations at different tube voltages, a combined image that is equivalent to an image to be obtained when a virtual tube voltage is radiated. The image processing method includes acquiring a plurality of radiographic images captured by irradiating a photographic subject with radiations at different tube voltages; acquiring information representing at least one region of interest selected in a radiographic image among the plurality of radiographic images and a first virtual tube voltage for the region of interest; deriving, for an unselected region other than the region of interest in the radiographic image, a second virtual tube voltage according to a distance from the region of interest; generating, for the region of interest, a first region image from the plurality of radiographic images, the first region image being equivalent to an image to be obtained when a radiation at the first virtual tube voltage is radiated; generating, for the unselected region, a second region image from the plurality of radiographic images, the second region image being equivalent to an image to be obtained when a radiation at the second virtual tube voltage is radiated; and generating a combined image obtained by combining the first region image and the second region image together.

An image processing program according to the present disclosure is an image processing program to be executed by a processor included in an image processing apparatus that generates, using a plurality of radiographic images captured by irradiating a photographic subject with radiations at different tube voltages, a combined image that is equivalent to an image to be obtained when a virtual tube voltage is radiated. The image processing program including acquiring a plurality of radiographic images captured by irradiating a photographic subject with radiations at different tube voltages; acquiring information representing at least one region of interest selected in a radiographic image among the plurality of radiographic images and a first virtual tube voltage for the region of interest; deriving, for an unselected region other than the region of interest in the radiographic image, a second virtual tube voltage according to a distance from the region of interest; generating, for the region of interest, a first region image from the plurality of radiographic images, the first region image being equivalent to an image to be obtained when a radiation at the first virtual tube voltage is radiated; generating, for the unselected region, a second region image from the plurality of radiographic images, the second region image being equivalent to an image to be obtained when a radiation at the second virtual tube voltage is radiated; and generating a combined image obtained by combining the first region image and the second region image together.

According to the present disclosure, an unnatural change in pixel values in a radiographic image can be suppressed.

DETAILED DESCRIPTION

An exemplary embodiment for implementing a technique of the present disclosure will be described in detail below with reference to the drawings.

First, a configuration of a radiographic image capturing system10according to the present embodiment will be described with reference toFIG.3. As illustrated inFIG.3, the radiographic image capturing system10includes an image processing apparatus12and an imaging apparatus14. Examples of the image processing apparatus12include a server computer or the like. The image processing apparatus12and the imaging apparatus14are connected to each other to be able to communicate with each other via a network.

The imaging apparatus14is an imaging apparatus that captures a radiographic image by irradiating a photographic subject with a radiation. The imaging apparatus14according to the present embodiment is capable of capturing a plurality of radiographic images by irradiating a photographic subject with radiations at different tube voltages. Specifically, the imaging apparatus14applies a first tube voltage (for example, 80 kVp) to a radiation source to irradiate a photographic subject with a radiation, and captures a first radiographic image based on the radiation that has passed through the photographic subject. The imaging apparatus14then applies a second tube voltage (for example, 140 kVp), which is higher than the first tube voltage, to the radiation source to irradiate the photographic subject with a radiation, and captures a second radiographic image based on the radiation that has passed through the photographic subject. In the present embodiment, a case will be described where a computed tomography (CT) apparatus is used as the imaging apparatus14. That is, the first radiographic image and the second radiographic image according to the present embodiment are CT images.

The image processing apparatus12generates, using a plurality of radiographic images captured by irradiating a photographic subject with radiations at different tube voltages, a combined image that is equivalent to an image to be obtained when a radiation at a virtual tube voltage is radiated.

A hardware configuration of the image processing apparatus12according to the present embodiment will be described next with reference toFIG.4. As illustrated inFIG.4, the image processing apparatus12includes a central processing unit (CPU)20, a memory21serving as a temporary storage area, and a storage unit22that is nonvolatile. The image processing apparatus12also includes a display23such as a liquid crystal display, an input device24such as a keyboard and a mouse, and a network interface (I/F)25to be connected to a network. The CPU20, the memory21, the storage unit22, the display23, the input device24, and the network I/F25are connected to a bus27.

The storage unit22is implemented by a hard disk drive (HDD), a solid state drive (SSD), a flash memory, or the like. An image processing program30is stored in the storage unit22serving as a storage medium. The CPU20reads out the image processing program30from the storage unit22, loads the image processing program30into the memory21, and executes the loaded image processing program30.

A functional configuration of the image processing apparatus12according to the present embodiment will be described next with reference toFIG.5. As illustrated inFIG.5, the image processing apparatus12includes a first acquisition unit40, a second acquisition unit42, a deriving unit44, a generation unit46, a combining unit48, and a display control unit50. The CPU20executes the image processing program30to function as the first acquisition unit40, the second acquisition unit42, the deriving unit44, the generation unit46, the combining unit48, and the display control unit50.

The first acquisition unit40acquires the first radiographic image and the second radiographic image captured by the imaging apparatus14.

The user selects, via the input device24, at least one region of interest in the first radiographic image or the second radiographic image displayed as a two-dimensional image on the display23. The user also inputs, via the input device24, a first virtual tube voltage for the selected region of interest. When the user selects a plurality of regions of interest, the user inputs the first virtual tube voltage for each of the regions of interest. For example, when the user desires to emphasize the contrast effect in the region of interest, the user inputs a relatively low tube voltage as the first virtual tube voltage. On the other hand, for example, when the user desires to reduce noise in the region of interest, the user inputs a relatively high tube voltage as the first virtual tube voltage.

The second acquisition unit42acquires information representing the at least one region of interest selected by the user as described above and the first virtual tube voltage for the region of interest input by the user as described above.

The deriving unit44derives, for an unselected region other than the region of interest in the first radiographic image or the second radiographic image, a second virtual tube voltage according to a distance from the region of interest. Specifically, the deriving unit44derives the second virtual tube voltage according to a distance from a centroid of the region of interest, using a function that outputs a tube voltage value that increases as the distance from the centroid of the region of interest increases. Thus, as illustrated inFIG.6as an example, the second virtual tube voltage for the unselected region becomes a voltage of a value that increases as the distance from the centroid of the region of interest increases, with respect to the first virtual tube voltage. In the example ofFIG.6, the first virtual tube voltage for the region of interest is 70 keV, and positions where the second virtual tube voltage for the unselected region becomes equal to 80 keV, 90 keV, and 100 keV are represented by respective broken lines.

The deriving unit44may derive the second virtual tube voltage according to the distance from the region of interest, using, for example, a look-up table in which the distance from the region of interest and the tube voltage are associated with each other, instead of the function described above.

When the second acquisition unit42acquires information representing a plurality of regions of interest, the deriving unit44derives, for the unselected region, the second virtual tube voltage according to a distance from a closest region of interest among the plurality of regions of interest. In one example, for a position P1 in the unselected region illustrated inFIG.7, the deriving unit44derives the second virtual tube voltage according to a distance D1 from a closest region of interest 1 among regions of interest 1 to 3. For a position P2 in the unselected region illustrated inFIG.7, the deriving unit44derives the second virtual tube voltage according to a distance D2 from the closest region of interest 3 among the regions of interest 1 to 3.

For the region of interest, the generation unit46generates, from the first radiographic image and the second radiographic image, a first region image equivalent to an image to be obtained when a radiation at the first virtual tube voltage is radiated. For the unselected region, the generation unit46generates, from the first radiographic image and the second radiographic image, a second region image equivalent to an image to be obtained when a radiation at the second virtual tube voltage is radiated.

A method of generating an image equivalent to an image to be obtained when a radiation at any virtual tube voltage is radiated will be described below. By performing a weighted calculation using two linear attenuation coefficients on two CT images, a CT image equivalent to an image to be obtained when a radiation at any virtual tube voltage is radiated can be generated.

A linear attenuation coefficient µ and a CT number have a relationship of Equation (1) below. µwaterin Equation (1) denotes a linear attenuation coefficient of water and is a known value.

First, it is assumed that a given substance is made of two base substances. Since water and iodine are often used as the two base substances, an example of using water and iodine as the two base substances will be described herein.

A linear attenuation coefficient µ at any tube voltage Eican be represented by Equation (2) below in which a product of a linear attenuation coefficient µ and a density C of water and a product of a linear attenuation coefficient µ and a density C of iodine, where water and the iodine are the two base substances, are added together.

The linear attenuation coefficients µwaterand µiodineof water and iodine at the any tube voltage Ei are known. Thus, if the densities Cwaterand Ciodineof water and iodine are known, the linear attenuation coefficient µ at the any tube voltage Ei can be determined.

The first radiographic image and the second radiographic image are used to determine the densities Cwaterand Ciodineof water and iodine. It is assumed that the first radiographic image is captured at a tube voltage E1, and the second radiographic image is captured at a tube voltage E2.

Linear attenuation coefficients µ1and µ2are determined from the first radiographic image and the second radiographic image in accordance with equation (1). From Equation (2), simultaneous equations represented by Equations (3) and (4) below hold.

By solving these simultaneous equations, the density Cwaterof water and the density Ciodineof iodine, which are unknown quantities, are determined. Since the densities Cwaterand Ciodineof water and iodine are determined, the linear attenuation coefficient at the any virtual tube voltage can be determined in accordance with equation (2). Once the linear attenuation coefficient µ at the any tube voltage Ei can be determined, the CT number at the any virtual tube voltage can be determined in accordance with equation (1).

The combining unit48generates a combined image obtained by combining the first region image and the second region image generated by the generation unit46together. The display control unit50performs control to display the combined image generated by the combining unit48on the display23. With the configuration described above, the first region image is generated for the region of interest, the second region image is generated for the unselected region, and the combined image obtained by combining the first region image and the second region image together is generated, as illustrated inFIG.8as an example.

An operation of the image processing apparatus12according to the present embodiment will be described next with reference toFIG.9. The CPU20executes the image processing program30, so that an image generation process illustrated inFIG.9is performed. The image generation process illustrated inFIG.9is performed, for example, in response to a user inputting an instruction to start the execution via the input device24.

In step S10inFIG.9, the first acquisition unit40acquires the first radiographic image and the second radiographic image captured by the imaging apparatus14. In step S12, the second acquisition unit42acquires information representing at least one region of interest selected by the user and the first virtual tube voltage for the region of interest input by the user, as described above.

In step S14, the deriving unit44derives, for an unselected region other than the region of interest represented by the information acquired in step S12, the second virtual tube voltage according to the distance from the region of interest, as described above. In step S16, for the region of interest, the generation unit46generates, from the first radiographic image and the second radiographic image, the first region image equivalent to an image to be obtained when a radiation at the first virtual tube voltage is radiated. In step S18, for the unselected region, the generation unit46generates, from the first radiographic image and the second radiographic image, the second region image equivalent to an image to be obtained when a radiation at the second virtual tube voltage is radiated.

In step S20, the combining unit48generates a combined image obtained by combining the first region image generated in step S16and the second region image generated in step S18together. In step S22, the display control unit50performs control to display the combined image generated in step S20on the display23. In response to the end of the processing of step S22, the image generation process ends.

As described above, according to the present embodiment, the first region image corresponding to the designated first virtual tube voltage is generated for the region of interest, and the second region image corresponding to the second virtual tube voltage according to the distance from the region of interest is generated for the region other than the region of interest. The combined image obtained by combining the first region image and the second region image together is then generated. Thus, an abrupt change in the tube voltage in the combined image is suppressed. Consequently, an unnatural change in pixel values in a radiographic image can be suppressed.

In the embodiment described above, for example, various processors mentioned below can be used as a hardware structure of processing units that perform various processes, such as the first acquisition unit40, the second acquisition unit42, the deriving unit44, the generation unit46, the combining unit48, and the display control unit50. The aforementioned various processors include, in addition to a CPU which is a general-purpose processor that executes software (program) to function as the various processing units as described above, a programmable logic device (PLD), such as a field programmable gate array (FPGA), which is a processor whose circuitry is changeable after production; a dedicated electric circuit, such as an application specific integrated circuit (ASIC), which is a processor having circuitry designed exclusively for executing specific processing; and the like.

A single processing unit may be constituted by one of these various processors, or by a combination of two or more processors of the same kind or different kinds (for example, a combination of a plurality of FPGAs or a combination of a CPU and an FPGA). In addition, a plurality of processing units may be constituted by a single processor.

Examples in which the plurality of processing units are constituted by a single processor include a first configuration, as exemplified by computers such as a server and a client, in which a combination of one or more CPUs and software constitutes the single processor and this processor functions as the plurality of processing units. The examples also include a second configuration, as exemplified by a System on Chip (SoC) or the like, in which the processor that implements functions of the entire system including the plurality of processing units on a single integrated circuit (IC) chip is used. As described above, the various processing units are constituted using one or more of the various processors above in terms of the hardware structure.

More specifically, electric circuitry in which circuit elements such as semiconductor elements are combined can be used in terms of the hardware structure of these various processors.

In the embodiment above, the configuration has been described in which the image processing program30is stored (installed) in the storage unit22in advance. However, the configuration is not limited to this. The image processing program30may be provided in a form of a recording medium, such as a compact disc read-only memory (CD-ROM), a digital versatile disc read-only memory (DVD-ROM), or a Universal Serial Bus (USB) memory, on which the image processing program30is recorded. The image processing program30may also be downloaded from an external apparatus via a network.