JPS6289173A - Medical picture information display method and its device - Google Patents

Abstract

PURPOSE:To improve a diagnostic performance and to rationalize a diagnostic operation by applying a non-sharp mask processing for emphasizing a frequency component having a prescribed extremely low space frequency or above continuously changing an emphasis coefficient and successively displaying on a display device as an animation picture. CONSTITUTION:An original signal memory 10 for storing an original picture signal Sorg, a non-sharp mask processor 20 for emphasizing a frequency component having the extremely low space frequency or above corresponding to a Sus by performing the operation of S'=Sorg+beta(Sorg-Sus), a controller 30 for successively changing at least one of the above-mentioned Sus and beta and a CRT device for successively displaying plural processing pictures based on a picture signal S' as moving pictures are provided. The various types of control informations are required to be inputted to the controller 30, herein, a control information input device 50 receives the various types of the informations from a host computer or a human being, converts into a suitable signal and outputs them to the controller 30.

Description

DETAILED DESCRIPTION OF THE INVENTION (Field of the Invention) The present invention relates to a method for displaying medical image information on a display device such as a cathode ray tube (hereinafter referred to as CRT) after subjecting medical image information to unsharp mask processing, and to implementing the method. It relates to a device for.

(Technical background of the invention and prior art) Certain types of phosphors are exposed to radiation (X-rays, α-rays, β-rays.

When irradiated with γ-rays, electron beams, ultraviolet rays, etc., part of the energy of this radiation is accumulated in the phosphor, and then when the phosphor is irradiated with excitation light such as visible light, it will respond to the accumulated energy. The phosphor exhibits stimulated luminescence. A phosphor exhibiting such properties is called a stimulable phosphor (stimulable phosphor).

Using this stimulable phosphor, radiation image information of a subject such as a human body is recorded on a stimulable phosphor sheet (hereinafter referred to as a stimulable phosphor sheet), and the sheet is scanned with excitation light. A radiographic image information recording and reproducing system has been proposed that generates stimulated luminescence, photoelectrically reads the stimulated luminescent light to obtain an image signal, and processes this image signal to obtain a radiographic image of a subject that is suitable for diagnosis ( For example, JP-A-55-124
No. 29.

Same 55-116340@, Same 55-163472
No. 56-11395.

5G-104645, etc.).

According to this system, radiation image information stored and recorded on a stimulable phosphor sheet is read in a charging manner, the electrical signal is subjected to appropriate signal processing, and this electrical signal is used to produce recording materials such as photographic light-sensitive materials. By outputting a radiation image as a visible image on a display device such as a CRT, a very large effect can be obtained in that a radiation image with excellent observation and interpretation suitability (diagnosis suitability) can be obtained.

One such signal processing method is, for example, Japanese Unexamined Patent Publication No. 55-1
There is a non-sharp mask processing method as described in Japanese Patent No. 63472.

Briefly, this method reads radiographic image information stored and recorded on the stimulable phosphor sheet in a charging manner by scanning an excitation light to generate an original image signal (electrical signal>5
ora, and obtain the unsharp mask signal Sus corresponding to the ultra-low spatial frequency for each scanning point of the stimulable phosphor sheet, set the emphasis coefficient to β, and use the calculation s'-5oro+β(5org-Sus). The present invention is characterized in that the signal is converted to emphasize frequency components (frequency bands) above the ultra-low spatial frequency, and this signal S' is used for forming the visible image.

This non-sharp mask processing method is extremely useful in that it increases the contrast of diagnostic objects (intrapulmonary canals, epiphyses, tumors, soft tissues, etc.), increases the efficiency of interpretation and diagnosis, and reduces the rate of missed lesions. This is a unique image processing method.

However, the conventional method of performing such unsharp mask processing and displaying the image as a visible image has the following problems.

In other words, when displaying a visible image after performing unsharp mask processing, it is customary to output and display it as a single still image on film, hard copy, or CRT. Displays only the result of emphasizing one type of frequency band using only one type of emphasizing coefficient.

However, the optimal values of these emphasis frequency bands and emphasis coefficients change even within the same image depending on the diagnostic purpose of the doctor. For example, if we take a fracture in a limb as an example, first of all, in order to properly diagnose the fracture line, etc., it is desirable to emphasize a relatively high frequency band to clearly depict the outline of the bone. In order to diagnose soft tissue inflammation, it is desirable to emphasize relatively low frequency bands.

Therefore, conventionally, when it is desired to perform a diagnosis by applying multiple unsharp mask processes to one image information under different conditions (emphasis frequency band and emphasis coefficient) as described above,
For example, ∎ a human being resets the above unsharp mask processing conditions one by one, and outputs images with different processing one by one onto film, hard copy, or CRT to find the optimal processing conditions, or ∎ Multiple images on one film, hard copy or one or two or three C
A method was adopted in which the images were displayed side by side on RT and used for diagnosis.

However, such conventional methods involve a large time loss because the process is redone once, and a large economic loss because multiple sheets of film are consumed (especially in the case of method ① above). It is difficult to output and display as many images as necessary at one time for diagnosis due to variations in the required mask processing conditions (especially when using method case), etc.

Therefore, when displaying multiple images that have been subjected to unsharp mask processing under different processing conditions, it is desirable to display more processed images more efficiently, improve diagnostic performance, and streamline diagnostic work. is desirable.

(Objective of the Invention) In view of the above circumstances, an object of the present invention is to provide a plurality of processed images in which unsharp mask processing is performed on one image information under different processing conditions (emphasis frequency band and emphasis coefficient). An object of the present invention is to provide a medical image information display method that can display more and more efficiently, improve diagnostic performance, and streamline diagnostic work, and an apparatus for implementing the method.

(Structure of the Invention) In order to achieve the above object, the medical image information display method according to the present invention scans a recording medium, reads out the medical image information recorded therein as an electric signal (original image signal), When displaying the medical image information as a visible image on a display device based on the original image signal, an unsharp mask signal Sus corresponding to a predetermined ultra-low spatial frequency at each scanning point is obtained, and the above-mentioned original image signal SO
rg, and the emphasis coefficient is β, S' = Sorv+
The calculation β(SOrQ −Sus) is performed to perform unsharp mask processing to emphasize the frequency components (frequency band) above the ultra-low spatial frequency and display the unsharp mask signal Sus or the emphasis coefficient β. The feature is that it is displayed as a moving image while changing continuously.

Further, the medical image information display device according to the present invention for implementing the above method includes an original image signal memory storing the above original image signal Sorg, and the above S′=Sorg+β(SOr
A non-sharp mask processing device that performs a calculation called "G-Sus" to perform non-sharp mask processing;
a control device that operates the unsharp mask processing device to sequentially change at least one of s and the emphasis coefficient β and perform the unsharp mask processing under each Sus or each β; Alternatively, the present invention is characterized by comprising a display device that continuously displays a plurality of images based on the image signal S' obtained by performing unsharp mask processing under each β as a moving image.

(Effects of the Invention) As described above, the medical image information display method and device according to the present invention, in short, performs the calculation s' = soro + β (Sorg -8uS) to display frequency components higher than a predetermined ultra-low spatial frequency. When displaying a visible image on the display i after performing the unsharp mask processing for emphasis, the unsharp mask signal S
The system continuously changes the Sus or the emphasis coefficient β, and continuously displays each non-sharp mask processed image under each changed Sus or each β as a moving image from time to time on a display device. Therefore, the diagnostic performance can be dramatically improved, and the diagnostic work can be streamlined.

That is, when outputting an image subjected to unsharp mask processing on a display device, a large number of processed images with different unsharp mask signals 5US (emphasis frequency band) and emphasis coefficients β are continuously outputted from time to time as a moving image. Since the images can be displayed, doctors can obtain and observe all the information and optimal images necessary for various diagnostic purposes, thereby dramatically improving diagnostic performance.

In addition, since multiple processed images are continuously displayed as moving images on one display device, it is possible to observe a large number of differently processed images in a short period of time. By setting the processing conditions one by one, each processed image is processed one by one on film, hard copy or CRT.
Diagnosis work can be streamlined without the hassle of displaying it on top.

Note that the display device referred to here refers to a device that can switch screens at a speed that humans visually perceive as a moving image, such as a CRT device, a liquid crystal display device, an electrochromic display device, a PLZT display device, and the like.

(Embodiments) Hereinafter, embodiments of the present invention will be described with reference to the drawings.

The medical image information display method and device according to the present invention scans a recording medium, reads out the medical image information recorded therein as an electrical signal, and displays the medical image information on a display device based on the electrical signal. In addition to displaying the image as a visual image, it is assumed that the electric signal read out above, that is, the original image signal 3 org, is displayed after being subjected to unsharp mask processing.

The recording medium may be, for example, the stimulable phosphor sheet or an X-ray photographic film. In short, any media may be used as long as it can record medical image information and ultimately read out the medical image information as an electrical signal by scanning the recording medium.

In the case of a stimulable phosphor sheet, the radiation that has passed through the object is made incident on the sheet, the sheet is scanned with excitation light such as a laser beam, and the stimulated luminescent light emitted from the sheet by this scanning is sent to a photomultiplier. etc., and the obtained electrical signal (original image signal 5o
The present invention is used when applying an appropriate non-sharp masking process to the Sorg when outputting a visible image on a display device such as a CRT based on the above-mentioned Sorg.rq).

In the case of X-ray photographic film, the image taken on the film is optically scanned, and the transmitted or reflected light is read photoelectrically using a photomultiplier, COD line sensor, etc. and converted into an electrical signal. The present invention is used when this electrical signal (original image signal 5 orq) is subjected to appropriate unsharp mask processing and then displayed as a visible image on a display device such as a CRT.

As mentioned above, in the unsharp mask processing, the unsharp mask signal SUS corresponding to the ultra-low spatial frequency at each scanning point is obtained, the emphasis coefficient is set to β, and the calculation s'-5oro+β(Sore-8US) is performed. , which emphasizes frequency components above the ultra-low spatial frequency.

Unsharp mask signal Sus corresponding to the ultra-low spatial frequency
is a non-sharp image (
This refers to the signal corresponding to the density at each scanning point of the "unsharp mask" (hereinafter referred to as "unsharp mask"). .5 or more and less than 0.5 at 0.5 cycles/willow spatial frequency, or 0.5 or more.
In the spatial frequency range of 0.01 to 0.5 cycles/mm, the integral value of the modulation transfer function with 0.001 as the lower end is 0.
．． A value that is 90% of the integral value of the modulation transfer function of 001 to 10 cycles/mm is used.

Further, as a method for creating this non-sharp mask, the following methods can be mentioned.

The first method is to store the original image signal at each scanning point, read it out together with peripheral data according to the size of the unsharp mask, and calculate the average value (simple average or average value based on various weighted averages) of Sus. This is a method to find.

In this method, the analog signal may be created as it is, or it may be created after A/D conversion as a digital signal. Furthermore, before A/D conversion, the analog signal is de-sharp using a low-pass filter only in the main scanning direction. The sub-scanning direction also includes cases in which digital signal processing is used.

The second method is to read out the original image signal using a light beam with a small diameter, etc., and then use a light beam with a large diameter that matches the size of the non-sharp mask to average the signal at each scanning point along with the surrounding signals. This is the method of reading the data. This method can be used only when the recording medium is a stimulable phosphor sheet and radiation image information still remains on the sheet after reading the original image signal.

The third method is a method that can be used when the recording medium is a stimulable phosphor sheet, and utilizes the fact that the beam diameter of the scanning light beam gradually expands due to scattering in the phosphor layer. , an original image signal Sorg is created by the light emission signal from the side where the light beam is incident, and an unsharp mask signal Sus is created by the light emission from the side through which the light beam passes. In this case, the size of the non-sharp mask can be controlled by changing the degree of light scattering of the phosphor layer or by changing the size of the aperture that receives the light.

In the method and apparatus according to the present invention, when displaying an image subjected to the unsharp mask processing as a visual image on a display device, the unsharp mask signal Sus or the emphasis coefficient β is continuously changed while the display device It is displayed as a moving image on the top.

That is, the above 5IJS or β is continuously varied in a range from a predetermined maximum value to a minimum value (continuous change in this case does not mean continuous change in the strict sense).
(This also includes cases in which the values change stepwise at appropriate small intervals), and using the values of each Sus or each β changed in this way, S'=Sora+β(S
org-Sus), and display a plurality of processed images based on the calculation results on a display device in sequence (in this case as well, continuous display in the strict sense means that a predetermined short (This also includes the case where the images are sequentially switched and displayed at time intervals), that is, the images are displayed continuously as a moving image.

Next, each actual t of the apparatus according to the present invention shown in FIGS.
Mode A will be explained.

The embodiment shown in FIG. 1 is based on the original image signal So
The original image signal memory 10 that stores rg, and non-sharp mask processing that performs the above calculation S'-8oro+β(Sorg-3u3) to emphasize frequency components (frequency bands) above the ultra-low spatial frequency corresponding to Sus. The unsharp mask processing device 20 performs the unsharp mask processing, and sequentially changes at least one of the Sus and β, and performs the unsharp mask processing under each changed Sus or β value. Control device for operating the device 20 @
30, and a CR that continuously displays a plurality of processed images based on the image signal S' obtained by performing unsharp mask processing under each Sus or each β value as a moving image.
T device 40.

The control device 30 has various control information, such as mode (Su
whether to change either s or β), the parameter (Su
It is necessary to input the change range of s or β), the step size of the change, the start or stop of the motion, etc. These control information may be input directly to the control Q device 30 via a human or a host computer, but the actual FM malicious mode is equipped with a control information input device 50, and the input device 50 inputs the various control information to the human. The controller 30 receives control information from a host computer, converts the control information into an appropriate signal, and outputs the signal to the control device 30.

The CRT device 40 includes a frame memory 42 that stores a processed image signal S' subjected to unsharp mask processing in the unsharp mask processing device 20 for one image, and a frame memory 42 that stores a signal outputted from the frame memory. It comprises a D/A converter 44 for converting data, and a CRT 4G for outputting and displaying a visible image based on the signal output from the D/A converter. That is, based on a predetermined SuS or When all processed image signals S' are stored, it is called CR.
It is output and displayed as a visible image on T, and then calculations and visual image display are performed in the same process based on the different Sus or β that have been changed. The J2 image display is switched one after another in an extremely short period of time and displayed as if it were a moving image.

This device has the advantage that there is no limit to the step of change of Sus or β, but on the other hand, the speed of image change on the CRT is limited by the calculation speed of the unsharp mask processing device 20.

In the embodiment shown in FIG. 2, multiple processed images calculated by the unsharp mask processing device 20 under each Sus or β value are stored in advance in the frame memory 42,
The address switch 48 is configured to switch the image displayed on the CRT 46 in units of one to several frames, and how the address switch 48 switches the address is inputted from the control information input device 50. It is controlled by the control device 30 based on the information obtained. The other configurations are similar to the embodiment shown in FIG.

This device can freely set the speed of image change on the CRT, but on the other hand, the storage capacity of the frame memory 42 limits the width of the change increments of Sus or β.

In the embodiment shown in FIG. 3, while both Sus and β are variable in the embodiment shown in FIGS. 1 and 2, only β is variable. That is, in this embodiment, the unsharp mask processing device 20 includes the arithmetic unit 21,
Consists of a memory 22, a multiplier 23, and an adder 24,
Since Sus is unchanged, first, the arithmetic unit 21 calculates Sorg-S.
The operation us is performed, the result is stored in the memory 22, the multiplier 23 performs the operation β×(SOr!+−Sus), and the adder 24 stores the result SOrg+β(Sorg−
Sus) is performed, and based on the result, a visible image is displayed by the CRT device 40 similar to the above. The above β is sequentially changed by the control device based on the control information inputted from the control information input device 50, and the plurality of processed images for each β thus changed are continuously displayed on the CRT device 40 as a moving image. will be displayed.

Although this device cannot change Sus, it can make small increments of β, and if you calculate Sorg -3US in advance and store it in the memory 24, all you need to do is multiply it by β and add it to Sorg. Therefore, a dedicated multiplier 23,
The provision of the adder 24 has the advantage that the image change speed can be increased.

The embodiment shown in FIG. 4 is based on the multiplication βx (Sorg-8US) and the addition WSOrg+β
(Sorg-Sus) is configured to perform analog calculations, and D/A converters 25 and 26 are used for this purpose.
(In this case, 22 is a frame memory).

The embodiment shown in FIG. 5 has a configuration in which both SuS and β are variable, whereas the embodiment shown in FIG. The embodiment is similar to the embodiment shown in FIG. 3, except that the Sus signal is input to the arithmetic unit 22 in order to also change the .

In this embodiment, there is almost no increment restriction for both 3us and β, and the image change speed due to changes in β is fast, but the image change speed due to changes in Sus is somewhat slow.

The embodiment shown in FIG. 6 is a second embodiment of the embodiment shown in FIG.
It incorporates a frame memory and an address switch shown in the figure, and stores Sorg-8IJS for each image calculated under each Sus value in the frame memory 27, and then switches the address switch. CRT46 by 28
It is constructed so that the image displayed above can be switched in units of one to several frenim, and β can also be changed.

In this device, there is almost no increment restriction on β, and the image change speed due to changes in β is fast, and Sus
You can freely adjust the speed of image change due to changes, but S
The increments of us changes are regulated by the storage capacity of the frame memory 27.

In the embodiment shown in FIG. 7, both SuS and β are variable, and although there is a limit to the step width of the Sus change, there is no problem in practical use, and the image change speed due to the Sus change is fast to some extent, which is extremely practical. It is a typical type of device.

This apparatus is particularly characterized by its unsharp mask processing device [20, which processing device 20 comprises an NXN
(N is an odd number, preferably N=3) size arithmetic unit 201 that calculates the unsharp mask signal Sus, a memory 202 that stores each unsharp mask signal Sus, and a control device 3
An arithmetic unit 203 calculates an unsharp mask signal Sus of a different mask size by suitably adding and averaging each unsharp mask signal Sus according to a command from 0, and 5IJS obtained in this way and an original image signal Sorg. a subtracter 204 that performs the operation Sorg −Sus between;
The output from the subtracter 204 is multiplied by β to obtain β(SOrfJ
-Sus), a multiplier 205 that performs the operation Sorg+β(S
The adder 206 performs the operation Or(+-Sus).

In this device, in order to obtain Sus at each scanning point, the SOrg at each scanning point is stored in memory, a rectangular non-sharp mask is prepared, and the size of the mask (the mask size is (represented by the length of two sides, and the length of each side is represented by the number of scanning points), reads 3 org of a predetermined scanning point and Sorgs of scanning points around the scanning point from the memory, Those! 111
fj! A method is used in which Sus regarding the above-mentioned predetermined scanning points is determined by averaging. In other words, Su at a given scanning point
To obtain s, prepare a rectangular unsharp mask of a predetermined size, and when the predetermined scan point is located in the center of the mask, simply add and average the 3 orgs of all the scan points located within the mask. It is determined by

In addition, in this case, changing or causing the above 5LI3 means SU
This means changing the size of the non-sharp mask when calculating S. That is, Sus is changed by sequentially changing the size of the non-sharp mask.

With these points understood, the embodiment shown in FIG. 7 will be described in more detail with reference to FIG. 8. In this device, a stimulable phosphor sheet, which is a recording medium, is first scanned with excitation light, and the original image signal 5 org at each scanning point (each square in Fig. 8 is one scanning point) is obtained. stored in the original image signal memory 10,
Next, an unsharp mask signal Sus of a mask size of 3×3 regarding each scanning point is calculated by a calculator? 01 and stores each Sus in the memory 202. For example, in FIG. 8, the unsharp mask signal S with mask size 3×3 regarding the scanning point
us is obtained by simply averaging 3 org of a total of nine scanning points (scanning point A is located in the center) included in the 3×3 unsharp mask Ma. The same applies to other scanning points. Using the Sus calculated in this way and stored in the memory, the subtracter 204 calculates Sorg.
-Sus, the computing unit 203 performs this l5
(activated only when changing us), multiplied by [1205
, the visible image is displayed on the CRT device 40 via the adder 206 as described above.

Next, the case where SuS is changed will be explained in detail.

As mentioned above, changing Sus means changing the non-sharp mask size, and in this device, the mask size is changed from the above-mentioned 3x3 to 9x9, 15x, etc.
15.21X21.27x27.・・・・・・・・・・・・
..., 111×111 and 19 types are changed in odd increments of 3, and the Sus for each mask size is projected. Sus with a mask size of 3×3 is stored in the memory 202 as described above1, and Sus with a mask size of 9×9 is stored in the memory 202 as described above.
To find us, use 9 3us of mask size 3x3. For example, in FIG. 8, when determining Sus with a mask size of 9×9 for scanning point A, a total of 9 SO3s for each mask M^~MI with a mask size of 3×3 are simply added and averaged by the calculator 203. required. Mask size 15x 15°21X21.
Similarly, when calculating each Sus of . . . , the S
It is obtained by simply adding and averaging 15, 21, etc. us.

The unsharp mask processed image based on each Sus obtained in this way is stored in the first frame memory 401 and the second frame memory 401.
The data is stored alternately in the frame memory 402, and from both frame memories is alternately sent to the CRT 46 via the D/A converter 44.
It is displayed as a visible image above. For example, mask size 3×
3 of 3 usl: While the processed image based on the first frame memory 401 is stored and the image is displayed on the CRT 46, the next processed image signal based on 5IJS with a mask size of 9×9 is stored in the second frame. The image is written into the memory 402, and when the processing is completed, the second frame memory 402 is connected to the D/A converter 44 and the image displayed on the CRT 46 is switched.

Calculations of different mask sizes Sus in the calculator 203 are performed based on commands from the control device 30.

A specific example of the role of the control device 30 will be explained below.

First, in the case of SuS change, Su
The receiver receives the information that there is a change in s and controls the mode. In this case, since it is a Sus change, β is fixed.

Next, conditions given to the control information input device 50 (for example, S
The necessary processing (the number of repetitions and the mask size for each processing (for example, 3x3, 9x9, 21x21, etc.)
・・・・・・・・・57x 57) etc. are calculated. Next, upon receiving a motion start signal from the control information input device 50, the entire apparatus is started through the synchronization line. When the calculation and image display with the first mask size are completed, the next mask size is applied to the necessary parts of the entire device and the next calculation and image display are started. When this process is repeated a predetermined number of times or when a motion start signal is received from the control information input device 50, the process is stopped and the current CR
Stops when T is displayed.

In the case of a β change, there is no need for complicated calculations as in the case of a Sus change, and the control device 30 simply controls the control device 20 based on information such as the change width received from the control information input device 50.
It is only necessary to change the multiplier β in 5.

In this implementation, Mr. M made it possible to increase the speed of image change based on the change even if the step width of the 8115 change is limited to some extent, so the size of the non-sharpening mask is only an odd multiple of 3 x 3. However, if there is a step width of this level, there is no problem in practice.

In addition, by using only odd multiples of 3×3 in this way, the mask signal Sus of each size can be obtained by simply averaging the mask signal Sus of mask size 3×3 as appropriate, which reduces the number of calculations. This makes it possible to reduce the speed of the calculation and thereby speed up the calculation.

As described above, in short, the method and apparatus according to the present invention sequentially display a plurality of processed images processed under different processing conditions (Sus or β) when displaying a non-sharp mask processed image on a display device. At the same time, a large number of processed images are sequentially switched and displayed at extremely short intervals to display them as if they were VJ images, and various modifications can be made as long as they do not exceed this range.

[Brief explanation of drawings]

1 to 7 are block diagrams showing an actual tM aspect of the medical image display device according to the present invention, and FIG. 8 is a diagram for explaining the Sus exclusion method in the embodiment shown in FIG. 7. be. 10...Original image signal memory 20...Unsharp mask processing device 30...Control II] device 40...CRT'a device 50...Control information input device 60...Recording medium 1st @ 4!0 2nd Flash Figure 4

Claims (2)

[Claims] (1) After scanning the recording medium and reading out the medical image information recorded therein and converting it into an electrical signal, the medical image information is displayed on the display device based on the original image signal obtained as the electrical signal. In order to display the image as a visible image, the unsharp mask signal Sus corresponding to the ultra-low spatial frequency at each scanning point was determined, the original image signal read from the recording medium was set as Sorg, and the emphasis coefficient was set as β. Sometimes, the calculation S'=Sorg+β(Sorg-Sus) is performed to display a non-sharp mask process that emphasizes the frequency components above the ultra-low spatial frequency, and the non-sharp mask signal Sus or the emphasis coefficient is A radiation image information display method characterized by displaying a moving image while continuously changing β. (2) Original image signal Sor obtained by scanning the recording medium and reading out the medical image information recorded on it
The original image signal memory that stores g, and the unsharp mask signal Sus corresponding to the ultra-low spatial frequency at each scanning point are obtained, the emphasis coefficient is set to β, and this Sus, β, and Sorg stored in the memory are used. , S'=Sorg+β(Sorg-Sus) A non-sharp mask processing device performs a non-sharp mask process that emphasizes frequency components higher than the ultra-low spatial frequency by performing the calculation: S'=Sorg+β(Sorg-Sus); a control device that operates the unsharp mask processing device to sequentially change at least one of the coefficient β and perform the unsharp mask processing under each Sus or each β; 1. A medical image information display device comprising: a display device that continuously displays a plurality of images as moving images based on the image signal S' obtained by performing unsharp mask processing under the following conditions.