JP2013111434A - Image processor, ultrasonic diagnostic apparatus and image processing program - Google Patents

Abstract

PROBLEM TO BE SOLVED: To facilitate an input operation to a medical image.SOLUTION: An ultrasonic diagnostic apparatus of an embodiment includes an input device 20, an acquisition part 171, an information storage part 183, a determination part 172, and a measurement part 173. The input device 20 receives specification of a measurement item using the medical image. The acquisition part 171 acquires a position in the medical image of a specified point specified on the medical image by an operator. The information storage part 183 stores a plurality of correction modes for correcting the position of the specified point on the basis of image information of a vicinity area in a prescribed range from the position of the specified point including the specified point in the medical image. The determination part 172 corrects the position of the specified point according to the prescribed correction mode determined on the basis of the measurement item, and determines the point of the corrected position as a correction point. The measurement part 173 performs measurement on the basis of the position of the correction point and the measurement item.

Description

  Embodiments described herein relate generally to an image processing apparatus, an ultrasonic diagnostic apparatus, and an image processing program.

  The ultrasonic diagnostic apparatus is less expensive and less exposed than other medical image diagnostic apparatuses such as an X-ray diagnostic apparatus and an X-ray CT (Computed Tomography) apparatus, and non-invasively displays an ultrasonic image indicating in-vivo information. Therefore, it plays an important role in today's medical care. Ultrasound diagnostic apparatuses are used in a wide range of fields such as diagnosis of circulatory organs such as the heart, diagnosis of abdominal organs such as the liver and kidney, diagnosis of peripheral blood vessels, diagnosis in obstetrics and gynecology, and diagnosis of breast cancer.

  Another feature of the ultrasonic diagnostic apparatus is portability. While most medical diagnostic imaging devices such as X-ray CT and MRI (Magnetic Resonance Imaging) devices are stationary, most ultrasonic diagnostic devices are equipped with operating wheels so that they can be transported. doing. Thereby, the ultrasonic diagnostic apparatus can be transported to the bedside of the ward in the hospital. Furthermore, in recent years, miniaturization of ultrasonic diagnostic apparatuses has been promoted. As such an ultrasonic diagnostic apparatus, for example, there is a hand carry type ultrasonic diagnostic apparatus (HCU: Hand Carry Ultrasound) that can be carried with one hand.

  Moreover, the form of the user interface is changing with the miniaturization of the ultrasonic diagnostic apparatus. For example, in an input device of a conventional ultrasonic diagnostic apparatus, a plurality of dedicated buttons are installed. However, at present, as with notebook personal computers (notebook PCs) typified by portable OA devices and information terminals with smartphone functions (smartphones), input buttons are virtually drawn on a liquid crystal monitor or the like. An ultrasonic diagnostic apparatus that employs an input form in which an operator clicks an input button (virtual button) with a mouse or a touchpad has been put into practical use. Furthermore, along with the practical use of monitors with touch sensors, so-called ultrasonic diagnostic apparatuses capable of so-called touch input, in which an operator performs an input operation by directly touching virtual buttons, have also been put into practical use. Note that devices capable of mouse input and touch input have been put to practical use in medical image diagnostic devices other than ultrasonic diagnostic devices.

  Mouse input and touch input are easy to accept for the operator because the operability is easy to interpret. For this reason, adopting mouse input or touch input in the medical image diagnostic apparatus has an advantage of improving the operability of the medical image diagnostic apparatus. On the other hand, when mouse input or touch input is employed in a medical image diagnostic apparatus, the following cases occur.

  For example, in the ultrasonic inspection, various measurements using an ultrasonic image are performed. The purpose of the measurement is various, but the elements of measurement include distance measurement performed by the operator specifying the position of two points, area measurement performed by drawing a closed curve by the operator, and the like. Many of these measurements require very fine accuracy. This is because, for example, the results of these measurements can be used to identify whether the tumor at the diagnostic site is malignant or benign, and the treatment policy and medication policy can be determined according to the results of the discrimination. Because.

  However, as experienced with a notebook PC or the like, for example, it is difficult for an operator to accurately trace an outline on a medical image using a mouse. Furthermore, in the case of touch input, it is difficult for an operator to accurately specify a point with a fingertip on a medical image.

JP 2009-153917 A

  The problem to be solved by the present invention is to provide an image processing apparatus, an ultrasonic diagnostic apparatus, and an image processing program that can facilitate an input operation on a medical image.

  The image processing apparatus according to the embodiment includes an input unit, an acquisition unit, a storage unit, a determination unit, and a measurement unit. The input unit accepts designation of measurement items using medical images. The acquisition unit acquires the position in the medical image of the designated point specified by the operator on the medical image. The storage unit stores a plurality of correction modes for correcting the position of the designated point based on image information of a neighboring region that includes the designated point in the medical image and is within a predetermined range from the position of the designated point. . The determination unit corrects the position of the designated point in accordance with a predetermined correction mode determined based on the measurement item, and determines the point of the corrected position as a correction point. The measurement unit performs measurement based on the position of the correction point and the measurement item.

FIG. 1 is a block diagram illustrating a configuration example of the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 2 is a diagram illustrating a configuration example of a control unit according to the first embodiment. FIG. 3 is a diagram (1) for explaining the process of the acquisition unit according to the first embodiment. FIG. 4 is a diagram (2) for explaining the process of the acquisition unit according to the first embodiment. FIG. 5 is a diagram illustrating an example of the input vicinity area set by the acquisition unit according to the first embodiment. FIG. 6 is a diagram for explaining a first determination method executed by the determination unit according to the first embodiment. FIG. 7 is a diagram for explaining a second determination method executed by the determination unit according to the first embodiment. FIG. 8 is a diagram (1) for explaining a modification of the first embodiment. FIG. 9 is a diagram (2) for explaining a modification of the first embodiment. FIG. 10 is a flowchart illustrating a processing procedure performed by the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 11 is a diagram illustrating a configuration example of a control unit according to the second embodiment. FIG. 12 is a diagram illustrating an example of prior information used in the second embodiment. FIG. 13 is a diagram (1) illustrating an example of processing of the estimation unit and the determination unit according to the second embodiment. FIG. 14 is a diagram (2) illustrating an example of processing of the estimation unit and the determination unit according to the second embodiment. FIG. 15 is a flowchart illustrating a processing procedure performed by the ultrasonic diagnostic apparatus according to the second embodiment. FIG. 16 is a diagram for explaining the third embodiment. FIG. 17 is a diagram for explaining a modification of the input vicinity area.

  Hereinafter, an embodiment of an ultrasonic diagnostic apparatus as an image processing apparatus will be described in detail with reference to the accompanying drawings.

(First embodiment)
First, the configuration of the ultrasonic diagnostic apparatus according to the first embodiment will be described. FIG. 1 is a block diagram illustrating a configuration example of the ultrasonic diagnostic apparatus according to the first embodiment. As illustrated in FIG. 1, the ultrasonic diagnostic apparatus 1 according to the first embodiment includes an ultrasonic probe 10, an input apparatus 20, a monitor 30, and an apparatus main body 100.

  The ultrasonic probe 10 includes a plurality of piezoelectric vibrators, and the plurality of piezoelectric vibrators generate ultrasonic waves based on a drive signal supplied from a transmission unit 110 included in the apparatus main body 100 described later. The ultrasonic probe 10 receives a reflected wave signal from the subject P and converts it into an electrical signal. The ultrasonic probe 10 includes a matching layer provided in the piezoelectric vibrator, a backing material that prevents propagation of ultrasonic waves from the piezoelectric vibrator to the rear, and the like. The ultrasonic probe 10 is detachably connected to the apparatus main body 100.

  When ultrasonic waves are transmitted from the ultrasonic probe 10 to the subject P, the transmitted ultrasonic waves are reflected one after another at the discontinuous surface of the acoustic impedance in the body tissue of the subject P, and the ultrasonic probe as a reflected wave signal Received by a plurality of piezoelectric vibrators 10. The amplitude of the received reflected wave signal depends on the difference in acoustic impedance at the discontinuous surface where the ultrasonic wave is reflected. Note that the reflected wave signal when the transmitted ultrasonic pulse is reflected on the moving blood flow or the surface of the heart wall depends on the velocity component of the moving body in the ultrasonic transmission direction due to the Doppler effect. And undergoes a frequency shift.

  In the first embodiment, even when the subject P is scanned two-dimensionally by the ultrasonic probe 10 which is a one-dimensional ultrasonic probe in which a plurality of piezoelectric vibrators are arranged in a row, the one-dimensional The ultrasonic probe 10 that mechanically swings a plurality of piezoelectric vibrators of the ultrasonic probe or the ultrasonic probe 10 that is a two-dimensional ultrasonic probe in which a plurality of piezoelectric vibrators are arranged two-dimensionally in a lattice shape is used. This is applicable even when the specimen P is scanned three-dimensionally.

  The input device 20 is connected to the device main body 100 and includes a mouse, a keyboard, a button, a panel switch, a touch command screen, a foot switch, a trackball, and the like. The input device 20 receives various setting requests from the operator of the ultrasonic diagnostic apparatus 1 and transfers the received various setting requests to the apparatus main body 100.

  For example, virtual operation buttons are drawn on the touch command screen (contact type screen) that is the input device 20. The operator inputs an instruction by pressing the operation button using a touch input method in which a virtual operation button is designated with a touch pen, a finger, or the like.

  The monitor 30 displays a GUI (Graphical User Interface) for an operator of the ultrasonic diagnostic apparatus 1 to input various setting requests using the input device 20, and displays an ultrasonic image generated in the apparatus main body 100. Or display. Specifically, the monitor 30 displays in-vivo morphological information and blood flow information as an image based on a video signal input from an image composition unit 160 described later.

  In the first embodiment, the monitor 30 also has a function as an input device. For example, in the first embodiment, the monitor 30 is made to be a contact type screen so that the monitor 30 functions as an input device. The operator can specify a point for distance measurement or draw a curve for area measurement on the ultrasonic image displayed on the monitor 30 by a touch input method using a touch pen or a finger, for example. can do. Further, the operator can specify a position for inserting a diagnostic report comment or an arrow on the ultrasonic image displayed on the monitor 30, for example, with a touch pen or a finger.

  The apparatus main body 100 generates an ultrasonic image based on the reflected wave signal received by the ultrasonic probe 10. As illustrated in FIG. 1, the apparatus main body 100 includes a transmission unit 110, a reception unit 120, a B-mode processing unit 131, a Doppler processing unit 132, an image generation unit 140, an image memory 150, an image composition, and the like. Unit 160, control unit 170, storage unit 180, and interface unit 190.

  The transmission unit 110 includes a pulse generator 111, a transmission delay unit 112, and a pulsar 113, and supplies a drive signal to the ultrasonic probe 10. The pulse generator 111 repeatedly generates rate pulses for forming transmission ultrasonic waves at a predetermined rate frequency. In addition, the transmission delay unit 112 focuses the ultrasonic wave generated from the ultrasonic probe 10 into a beam shape, and the pulse generator 111 determines the delay time for each piezoelectric vibrator necessary for determining the transmission directivity. For each rate pulse that occurs. The pulser 113 applies a drive signal (drive pulse) to the ultrasonic probe 10 at a timing based on the rate pulse. That is, the transmission delay unit 112 arbitrarily adjusts the transmission direction of the ultrasonic wave transmitted from the piezoelectric vibrator surface by changing the delay time given to each rate pulse.

  The receiving unit 120 includes a preamplifier 121, an A / D (Analog / Digital) converter (not shown), a reception delay unit 122, and an adder 123, and performs various processes on the reflected wave signal received by the ultrasonic probe 10. To generate reflected wave data. The preamplifier 121 amplifies the reflected wave signal for each channel. An A / D converter (not shown) A / D converts the amplified reflected wave signal. The reception delay unit 122 gives a delay time necessary for determining the reception directivity. The adder 123 performs an addition process on the reflected wave signal processed by the reception delay unit 122 to generate reflected wave data. By the addition process of the adder 123, the reflection component from the direction corresponding to the reception directivity of the reflected wave signal is emphasized, and a comprehensive beam for ultrasonic transmission / reception is formed by the reception directivity and the transmission directivity.

  The form of the output signal from the receiving unit 120 can be selected from various forms such as a signal including phase information called an RF (Radio Frequency) signal or amplitude information after envelope detection processing. Is possible.

  The B-mode processing unit 131 receives the reflected wave data from the receiving unit 120, performs logarithmic amplification, envelope detection processing, and the like, and data in which the signal intensity of each scanning line is expressed by brightness (B-mode data) Is generated.

  The Doppler processing unit 132 performs frequency analysis on velocity information from the reflected wave data received from the receiving unit 120, extracts blood flow, tissue, and contrast agent echo components due to the Doppler effect, and blood flow information such as average velocity, dispersion, and power. Are extracted for multiple points of each scanning line (Doppler data).

  The image generation unit 140 generates an ultrasonic image from the B-mode data generated by the B-mode processing unit 131 and the Doppler data generated by the Doppler processing unit 132, and the generated ultrasonic image is stored in the image memory 150 or the storage described later. Stored in the unit 180.

  Specifically, the image generation unit 140 generates a B-mode image in which the intensity of the reflected wave data is expressed by luminance from the B-mode data. Further, the image generation unit 140 generates a color Doppler image that displays the average blood flow velocity, the variance, the blood flow volume, and a combination thereof from the Doppler data so as to be identifiable by color.

  The image generation unit 140 converts (scan converts) a plurality of scanning line signal sequences for ultrasonic scanning into a scanning line signal sequence in a video format typified by a television or the like, and an ultrasonic image (B Mode image or color Doppler image). In addition, the image generation unit 140 is equipped with a storage memory (not shown) that stores image data. For example, after diagnosis, an operator can call up an image recorded during an examination.

  The image memory 150 is a memory that stores data received from the B-mode processing unit 131 and the Doppler processing unit 132. The data stored in the image memory 150 can be called by an operator after diagnosis, for example, and becomes an ultrasonic image for display via the image generation unit 140. This ultrasonic image can be reproduced as a still image or as a moving image using a plurality of images.

  The image memory 150 can also store an ultrasonic image generated by the image generation unit 140 and image data generated by performing image processing on the ultrasonic image. Such image data can also be reproduced as a still image or as a moving image using a plurality of images, for example, by an operator calling from the image memory 150 after diagnosis.

  The image composition unit 160 generates a composite image in which character information, scales, body marks, and the like of various parameters are combined with the ultrasonic image generated by the image generation unit 140. The composite image generated by the image composition unit 160 is displayed on the monitor 30.

  The control unit 170 is a control processor (CPU: Central Processing Unit) that realizes a function as an information processing apparatus (computer), and controls the entire processing in the ultrasonic diagnostic apparatus 1. Specifically, the control unit 170 is based on various instructions and setting requests input from the operator via the input device 20, a program read from the storage unit 180, which will be described later, and various setting information. 120, the B mode processing unit 131, the Doppler processing unit 132, the image generation unit 140, and the image synthesis unit 160 are controlled. In addition, the control unit 170 controls the monitor 30 to display an ultrasonic image or the like stored in the storage unit 180 or the image memory 150 described later.

  The storage unit 180 includes various programs 181 that store various programs for performing ultrasonic transmission / reception, image processing, and display processing, an image storage unit 182 that stores ultrasonic images generated by the image generation unit 140, and diagnostic information. (For example, patient ID, doctor's findings, etc.), an information storage unit 183 that stores various data such as a diagnostic protocol and various setting information.

  For example, the various programs 181 store a measurement program in which a procedure for performing measurement processing using an ultrasound image is described. Further, the various programs 181 store an image processing program in which a procedure executed by the control unit 170 described later is described. Various data stored in the storage unit 180 can be transferred to an external peripheral device via the interface unit 190.

  The interface unit 190 is an interface related to an operation panel (the input device 20 or the monitor 30 as an input device), an external storage device, and a network. Information received by the input device 20 and the monitor 30 as an input device is transferred to the control unit 170. Further, data such as an ultrasound image obtained by the ultrasound diagnostic apparatus 1 can be transferred to another apparatus via the network by the interface unit 190.

  The transmitter 110 and the ultrasonic receiver 120 built in the apparatus main body 100 may be configured by hardware such as an integrated circuit, but may be realized by a software modularized program. is there.

  The overall configuration of the ultrasonic diagnostic apparatus 1 according to the first embodiment has been described above. Here, in the ultrasonic inspection, various measurements using an ultrasonic image are performed. Examples of such measurement include distance measurement performed by the operator specifying two positions, area measurement performed by drawing a closed curve by the operator, and the like. Depending on the result of the measurement, whether the tumor at the diagnosis site is malignant or benign is differentiated, and the treatment policy and medication policy are determined according to the discrimination result. Measurement accuracy is required.

  However, it is possible to accurately trace the contour of a complex tumor site on an ultrasonic image displayed on the monitor 30 using the mouse of the input device 20, a touch pen, or a finger, or to specify an accurate measurement point reliably. It is difficult.

  For this reason, the ultrasonic diagnostic apparatus 1 according to the first embodiment performs the processing of the control unit 170 described below in order to facilitate the input operation on the ultrasonic image. That is, the control unit 170 according to the first embodiment acquires the position in the ultrasound image of the designated point designated on the ultrasound image by the operator. Then, the control unit 170 corrects the position of the designated point on the basis of the image information of the neighboring area including the designated point in the ultrasonic image and within the predetermined range from the position of the designated point. And the control part 170 determines the point of the corrected position as a correction point.

  Hereinafter, the control unit 170 according to the first embodiment will be described in detail with reference to FIG. FIG. 2 is a diagram illustrating a configuration example of a control unit according to the first embodiment.

  As illustrated in FIG. 2, the control unit 170 according to the first embodiment includes an acquisition unit 171, a determination unit 172, and a measurement unit 173. The processing of the acquisition unit 171 and the determination unit 172 described below is performed after an ultrasonic image designated by the operator via the input device 20 is displayed on the monitor 30 from the image storage unit 182.

  As described above, the acquisition unit 171 acquires the position of the designated point designated on the ultrasonic image by the operator. 3 and 4 are diagrams for explaining processing of the acquisition unit according to the first embodiment. For example, as shown in FIG. 3A, the monitor 30 displays an ultrasonic image 40 in which the outline of the tissue is drawn with a low-brightness black curve. The operator refers to the ultrasonic image 40 displayed on the monitor 30 and designates a point for distance measurement and a point for inserting an arrow for a diagnostic report on the contour. Such a point is designated by the operator using the mouse of the input device 20, for example. Alternatively, for example, it is specified by the operator pressing the contact type screen of the monitor 30 with a finger. In the ultrasonic image 40, the outline of the tissue is depicted with a low-brightness black curve.

  FIG. 3B is an enlarged view in which, in the ultrasonic image 40 shown in FIG. 3A, a region including a point of interest by the operator is schematically enlarged to a pixel (pixel) level. In FIG. 3B, the luminance value for each pixel is indicated by the dot density. In FIG. 3B, the lower the luminance value, the higher the dot density. Here, the pixel 51 and the pixel 52 are pixels depicted as an outline in the ultrasonic image 40 illustrated in FIG. Here, the pixel 52 having the lowest luminance value and located on the leftmost in the contour is set as a correct point (correct point) that the operator wanted to designate.

  For example, when the pixel 52 that is the correct answer point is designated with the mouse, the tip of the mouse cursor can usually indicate one pixel. In the case of mouse input, the acquisition unit 171 acquires the position of the point designated by the mouse as the position of the designated point. However, in the case of mouse input, the operator can move the mouse cursor to the pixel 52, but in order to specify the pixel 52 accurately, the operator carefully operates the mouse over time. There is a need. For this reason, the designated point designated by the mouse input may not necessarily be the pixel 52 which is the correct answer point.

  Furthermore, for example, in the case of touch input with a fingertip, the area where the fingertip touches the contact-type screen is widened, so that it is difficult to specify the pixel 51 that is the correct answer no matter how careful the operator operates. .

  In the case of touch input by a fingertip, the area touched by the operator's fingertip on the contact-type screen of the monitor 30 is not a single pixel, for example, an area 531 composed of a plurality of pixels surrounded by a solid line in FIG. It becomes. In the case of touch input, the acquisition unit 171 acquires the position of the pixel corresponding to the position where the fingertip is first touched on the contact type screen as the position of the designated point. Alternatively, the acquisition unit 171 acquires the position of the pixel corresponding to the barycentric position of the region 531 as the position of the designated point. For example, as illustrated in FIG. 4B, the acquisition unit 171 acquires not the pixel 52 but the pixel 53 positioned to the right of the pixel 52 as the designated point, and obtains the position of the pixel 53 as the designated point position.

  The determination unit 172 illustrated in FIG. 2 sets image information of a neighboring area that includes the designated point and is within a predetermined range from the position of the designated point. Specifically, the information storage unit 183 shown in FIG. 2 corrects the position of the designated point based on the image information of a neighboring region that includes the designated point in the ultrasonic image and is within a predetermined range from the position of the designated point. Multiple correction modes are stored. Then, the determination unit 172 selects one correction mode from among a plurality of correction modes, corrects the position of the designated point, and determines the point at the corrected position as the correction point. Hereinafter, the above-described neighboring area is referred to as “input neighboring area”. For example, the position in the ultrasonic image 40 of the pixel 53 that is the designated point is (x, y). The determination unit 172 sets the input neighborhood area using the coefficient “a” stored in the information storage unit 183. The coefficient “a” is a set value set in advance as a value for setting a predetermined range. Alternatively, the coefficient “a” may be set by the operator when the ultrasound image 40 is read. FIG. 5 is a diagram illustrating an example of the input vicinity area set by the acquisition unit according to the first embodiment.

  For example, it is assumed that the setting value “4 (unit: pixel)” is stored in the information storage unit 183. In such a case, as illustrated in FIG. 5, the determination unit 172 has “(x−4, y−4), (x + 4, y−4), (x−4, y + 4), (x + 4, y + 4)” as a vertex. Is set as an input vicinity area. The pixel 53 that is the designated point and the pixel 52 that is the correct answer point are included in the square area 54 set as the input vicinity area. Note that an arbitrary value can be set as the value of “a”, and the unit of “a” can be arbitrarily set, for example, a length. Further, the shape of the input vicinity area can be set to an arbitrary shape such as a rectangle, a circle, an ellipse, or a ring.

  Then, the determination unit 172 corrects the position of the designated point based on the image information of the input vicinity area, and determines the pixel at the corrected position as the correction point. Specifically, the determination unit 172 selects one correction mode from among a plurality of correction modes, corrects the position of the designated point, and determines the point at the corrected position as the correction point. More specifically, the determination unit 172 selects one correction mode from among a plurality of correction modes based on the image information in the input vicinity area. The correction point determined by the determination unit 172 is a point where the correct point is estimated based on the image information in the input vicinity area. Hereinafter, two determination methods performed by the determination unit 172 will be described. The following two determination methods are determination methods based on the correction mode selected by the determination unit 172.

  First, the first determination method will be described. As a first determination method, the determination unit 172 determines a correction point based on the distribution of luminance values of pixels that constitute the input vicinity area. In other words, the determination unit 172 is “at least one of a plurality of correction modes stored in the information storage unit 183,“ a correction mode for determining a correction point based on the distribution of luminance values of pixels constituting the input neighborhood area ”. Select. FIG. 6 is a diagram for explaining a first determination method executed by the determination unit according to the first embodiment.

  The first determination method is a method based on the fact that the brightness value of the contour part is usually different from the periphery of the contour part as in the region 54 where the distribution of the brightness value is biased. In this method, the point at which the luminance value is maximized or the point at which the luminance value is minimized is used as the correction point.

  First, when the first determination method is executed, the determination unit 172 adopts a point where the luminance value is maximum from the distribution of luminance values in the input vicinity area as a correction point, or corrects a point where the luminance value is minimum. Determine whether to adopt as a point.

  For example, the determination unit 172 generates a profile in a predetermined direction of the luminance value of the pixels constituting the input vicinity area. For example, when the predetermined direction is the horizontal direction (the azimuth direction of the ultrasonic image), the determination unit 172 uses the region 54 to obtain nine horizontal luminance profiles as illustrated in FIG. Generate. As shown in FIG. 6A, the determination unit 172 has a valley shape in which the shape of each of the nine luminance profiles protrudes downward, that is, the low luminance value is low in each of the nine luminance profiles. Therefore, it is determined that the point having the minimum luminance value is adopted as the correction point.

  Note that the determination unit 172 generates not only the horizontal direction but also the profile in the vertical direction (depth direction of the ultrasonic image) and the oblique direction, and performs the above-described determination processing from the profile shapes in a plurality of predetermined directions. May be.

  Then, as illustrated in FIG. 6B, the determination unit 172 determines the pixel 52 that is the point at which the luminance value is minimum in the nine luminance profiles as the correction point. That is, the determination unit 172 estimates the correct point of the designated point “pixel 53” as the correction point “pixel 52”. If it is determined that the point with the maximum luminance value is adopted as the correction point, the determination unit 172 determines the pixel with the maximum luminance value as the correction point.

  The control unit 170 changes “pixel 53” designated by the operator to “pixel 52” and displays it on the monitor 30. 3 performs measurement based on the position of the correction point and the measurement item specified by the operator.

  In addition, the method of determining adoption may be performed by the following method. For example, the determination unit 172 generates a histogram of luminance values in the input neighborhood area. Then, the determination unit 172 calculates the number of high-brightness pixels and the number of low-brightness pixels from the threshold value of the luminance value set to high luminance and the threshold value of the luminance value set to low luminance. Then, the determination unit 172 calculates a ratio or difference value between the number of high luminance pixels and the number of low luminance pixels, and compares the ratio or difference value with a predetermined threshold for determination. As a result of the comparison processing, the determination unit 172 determines that the point having the minimum luminance value is adopted as the correction point when the high-luminance pixels are frequent. Further, as a result of the comparison processing, the determination unit 172 determines that the point having the maximum luminance value is adopted as the correction point when the low-luminance pixels are frequently used in the histogram.

  For example, the determination unit 172 determines that the number of pixels “68” of the high luminance pixels (white pixels in the region 54 illustrated in FIG. 5) is the low luminance pixels (white in the region 54 illustrated in FIG. 5) from the luminance value histogram of the region 54. Since the number of pixels other than pixels) is greater than “13” and the difference value “55” is greater than the determination threshold value “50”, it is determined that the point having the minimum luminance value is adopted as the correction point.

  When there are a plurality of points where the luminance value is an extreme value and there are a plurality of candidate points for correction points, the determination unit 172 uses, for example, the point closest to the specified point that is the center of the input vicinity area as the correction point. decide. Or the determination part 172 may determine a correction point from several candidate points using the information of the measurement mode which the operator designated, for example. That is, the input device 20 accepts designation of measurement items for ultrasonic images. Then, the acquisition unit 171 acquires the position of the specified point, and the determination unit 172 corrects the position of the specified point according to a predetermined correction mode determined based on the measurement item, and the corrected position point is corrected. Determine as. For example, it is assumed that the measurement item designated by the operator is distance measurement and two designated points are acquired. The determination unit 172 determines a plurality of candidate points by the first determination method. Then, the determination unit 172 acquires the direction of the line segment connecting the two specified points according to the correction mode when the distance measurement mode is specified in the first determination method in the correction mode of the first determination method. The candidate point closest to the specified point in the acquired direction is determined as the correction point.

  Next, the second determination method will be described. As a second determination method, the determination unit 172 determines a correction point based on the spatial differentiation of the luminance values of the pixels constituting the input vicinity area. That is, the determination unit 172 is at least one of a plurality of correction modes stored in the information storage unit 183. “A correction mode in which a correction point is determined based on a spatial differentiation of luminance values of pixels constituting an input neighborhood area. ”Is selected. The second determination method is useful when a boundary portion where the luminance value changes is designated. FIG. 7 is a diagram for explaining a second determination method executed by the determination unit according to the first embodiment.

  First, even when the second determination method is executed, the determination unit 172 sets an input vicinity area. For example, it is assumed that the position of the pixel 55 that is the designated point is output from the acquisition unit 171 as illustrated in FIG. In such a case, as shown in FIG. 7A, the determination unit 172 sets a region 56 as an input neighborhood area from the position of the pixel 55 that is the designated point. As shown in FIG. 7A, the region 56 has a boundary formed by two regions having different luminance values.

  The determination unit 172 calculates a spatial differential for the region 56. Then, for example, as illustrated in FIG. 7B, the determination unit 172 generates an image having a spatial differential value (absolute value thereof) as a pixel value. In the image shown in FIG. 7B, the boundary portion is drawn with a white line.

  For example, as illustrated in FIG. 7C, the determination unit 172 has a convex shape on the left side that is close to the pixel 55 that is the designated point, and thus is positioned on the left side of the pixel 55 that is the designated point. Thus, the pixels forming the boundary portion are searched. Accordingly, as illustrated in FIG. 7C, the determination unit 172 sets four pixels A to D having the same horizontal position and different vertical positions as correction point candidate points.

  Here, the determination unit 172 determines the pixel C closest to the pixel 55 that is the designated point as a correction point. Alternatively, as described above, the determination unit 172 may determine correction points from a plurality of candidate points using information on measurement items specified by the operator. That is, the input device 20 accepts designation of measurement items for ultrasonic images. Then, the acquisition unit 171 acquires the position of the specified point, and the determination unit 172 corrects the position of the specified point according to a predetermined correction mode determined based on the measurement item, and the corrected position point is corrected. Determine as. For example, it is assumed that the measurement mode designated by the operator is distance measurement and two designated points are acquired. The determination unit 172 determines a plurality of candidate points by the second determination method. For example, the determination unit 172 is a correction mode of the second determination method, and determines two specified points specified in the distance measurement according to the correction mode when the distance measurement mode is specified in the second determination method. In the direction of the connecting line segment, the pixel B closest to the pixel 55 as the designated point is determined as a correction point. The control unit 170 changes “pixel 55” designated by the operator to “pixel B” and displays it on the monitor 30. 3 performs measurement based on the position of the correction point and the measurement item specified by the operator.

  As described above, the control unit 170 according to the first embodiment automatically corrects the designated position only when the operator designates a point roughly. In the above description, the case where a point is designated by the operator has been described. However, the first embodiment is applicable even when, for example, a curve for area measurement is drawn by the operator. . 8 and 9 are diagrams for explaining a modification of the first embodiment.

  For example, as shown in the left diagram of FIG. 8, the operator sets an elliptical curve 57 on the surface of the screen of the monitor 30 in order to measure the area of a small elliptical part in the saddle-shaped tumor part. Draw appropriately with your finger. In such a case, the acquisition unit 171 uses the curve 57 specified by the operator as a set of a plurality of specified points, and acquires the positions of the plurality of specified points. The determination unit 172 sets an input neighborhood area centered on each of a plurality of designated points, thereby setting a region 58 that is a set of input neighborhood areas as shown in the middle diagram of FIG.

  Then, the determination unit 172 executes the first determination method and the second determination method in the region 58 to determine a correction curve 59 that is a set of correction points as shown in the right diagram of FIG. . In the region 58, there is a part where no boundary exists. Therefore, the correction curve 59 indicated by a solid line is an open curve having end points as shown in the right diagram of FIG. On the other hand, the curve 57 designated by the operator is a closed curve as shown in the left diagram of FIG.

  Therefore, the determination unit 172 determines a set of correction points that form an interpolation curve 591 that smoothly connects the two end points of the correction curve 59. Then, the determination unit 172 finally outputs the correction curve 59 and the interpolation curve 591, and the control unit 170 causes the monitor 30 to display the correction curve 59 and the interpolation curve 591.

  Further, the first embodiment may be a case where the acquisition unit 171 performs the following interpolation processing. In the example shown in FIG. 9, the operator draws a thick open curve 571 roughly with a finger on the closed boundary portion. In such a case, the acquisition unit 171 acquires the positions of a plurality of designated points that form the open curve 571, and sets designated points that form an interpolation curve that connects two designated points corresponding to the two end points of the open curve 571. To do. Then, the acquisition unit 171 outputs the positions of a plurality of designated points that form a closed curve to the determination unit 172. The determination unit 172 sets an input neighborhood area from the positions of a plurality of designated points that are closed curves. Then, the determination unit 172 determines a correction curve 592 that is a set of correction points, as shown in FIG. The correction mode for performing the determination method described with reference to FIGS. 8 and 9 is also stored in the information storage unit 183.

  Next, a procedure of processing performed by the ultrasonic diagnostic apparatus 1 according to the first embodiment will be described with reference to FIG. FIG. 10 is a flowchart illustrating a processing procedure performed by the ultrasonic diagnostic apparatus according to the first embodiment. In FIG. 10, processing after the ultrasonic image is displayed on the monitor 30 will be described.

  As illustrated in FIG. 10, the control unit 170 of the ultrasonic diagnostic apparatus 1 determines whether or not an input of a designated point has been received from the operator (step S <b> 101). Here, when the input of the designated point is not accepted (No at Step S101), the control unit 170 waits until the designated point is accepted.

  On the other hand, when the input of the designated point is received (Yes at Step S101), the acquisition unit 171 obtains the position of the designated point (Step S102). And the determination part 172 sets an input vicinity area from the position of a designated point (step S103).

  Then, the determination unit 172 corrects the position of the designated point based on the image information in the input vicinity area, and determines the correction point (step S104). And the monitor 30 displays a correction point (step S105), and complete | finishes a process. Although not shown, measurement processing of the measurement unit 173 is performed after step S104. Note that the monitor 30 may be configured to display the designated point and the correction point at the same time after changing the color, for example, when the positions of the designated point and the correction point are different under the control of the control unit 170. .

  As described above, in the first embodiment, even if the point designated by the operator is an area composed of a plurality of points, a representative point is designated as the designated point in the area, and the position of the designated point is acquired. To do. In the first embodiment, an input vicinity area including the designated point is set on the ultrasonic image from the position of the obtained designated point. In the first embodiment, the correction point is determined by performing edge processing using the distribution of luminance values and differential values only in the input vicinity area.

  In other words, in the first embodiment, by performing local edge processing in an input vicinity area centering on a designated point that is estimated to be located in the vicinity of the correct answer point, the load required for the processing is reduced and the correct answer point is reduced. It is possible to accurately determine a correction point that estimates.

  As described above, in the first embodiment, only when the designated point is specified by roughly inputting a point or a curve, as in the case where the designated point is designated by finger input on the touch panel of the operator. Since the designated point and the designated curve which is a set of designated points are automatically corrected with high accuracy, the input operation for the ultrasonic image can be facilitated.

(Second Embodiment)
In the second embodiment, a method will be described in which the determination unit 172 changes a correction mode, that is, a method used for determining a correction point in accordance with the purpose for which the operator inputs a designated point.

  An ultrasonic diagnostic apparatus 2 according to the second embodiment will be described. Since the configuration of the ultrasonic diagnostic apparatus 2 according to the second embodiment is substantially the same as the configuration of the ultrasonic diagnostic apparatus 1 illustrated in FIG. 1, illustration thereof is omitted. However, the configuration of the control unit 170 according to the second embodiment is different from the control unit 170 according to the first embodiment shown in FIG. FIG. 11 is a diagram illustrating a configuration example of a control unit according to the second embodiment.

  As illustrated in FIG. 11, the control unit 170 according to the second embodiment includes an estimation unit 174 in addition to the acquisition unit 171 and the determination unit 172. Note that the acquisition unit 171 according to the second embodiment acquires the position of the designated point, as in the first embodiment.

  The estimation unit 174 shown in FIG. 11 estimates the purpose for which the operator has input the designated point based on the prior information regarding the ultrasound image input before the designated point is input. That is, the estimation unit 174 obtains prior information regarding the ultrasonic image displayed on the monitor 30 in order to input the designated point from the information storage unit 183, and estimates the input purpose of the designated point.

  That is, in the second embodiment, the estimation unit 174 estimates the input purpose using “prior information” which is not “direct information” which is information directly indicating the input purpose from the operator, and the determination unit 172 Then, the correction point determination algorithm is changed from the estimated input purpose.

  Hereinafter, the “preliminary information” will be described. The above "direct information" is a declaration of specific items of measurement. For example, when the operator presses a “Doppler automatic trace” button, the input purpose is “to trace the contour of the Doppler waveform”. For example, when the operator presses the “measure follicle area” button, the input purpose is “automatically recognize the follicular boundary to calculate the area”. Research results have been reported for automation algorithms specialized for these various purposes, and some algorithms have been put into practical use.

  On the other hand, the “preliminary information” used in the present embodiment is information input in advance to the ultrasonic diagnostic apparatus 2 as clinical examination information, for example, information illustrated in FIG. FIG. 12 is a diagram illustrating an example of prior information used in the second embodiment. For example, as shown in FIG. 12, the item “prior information” is “diagnosis region, disease region” where the subject P consults. Specific information input to “diagnosis area, disease area” includes, for example, “breast cancer screening”, “hepatic tumor screening”, and the like, as shown in FIG.

  Further, for example, the item “prior information” is “installation environment” in which the ultrasonic diagnostic apparatus 2 is installed as shown in FIG. Specific information input to the “installation environment” includes, for example, “dedicated apparatus for vascular system diagnosis” and “dedicated apparatus for breast cancer screening” as shown in FIG. Further, for example, as shown in FIG. 12, the item “prior information” is “preset” which is data initially set by the operator as an annotation of an ultrasonic image at the time of photographing. Specific information input to “preset” includes, for example, “heart”, “liver”, “thyroid”, etc., as shown in FIG.

  Further, for example, the item “prior information” is “probe type” which is information on the type of the ultrasonic probe 10 used for imaging as shown in FIG. Specific information input to “probe type” includes, for example, “3 MHz probe for abdomen” and “12 MHz probe for mammary gland” as shown in FIG.

  The estimation unit 174 estimates the input purpose from the prior information illustrated in FIG. For example, when the “installation environment” is “a device dedicated to vascular system diagnosis”, the estimation unit 174 estimates in advance that the operator inputs a designated point in order to perform measurement related to the blood vessel. Alternatively, for example, when the “probe type” is “12 MHz probe for mammary gland”, the estimation unit 174 presumes that the operator inputs a designated point in order to perform measurement related to the mammary gland. Alternatively, for example, when “preset” is “liver”, the estimation unit 174 estimates in advance that an operator inputs a designated point in order to perform measurement related to the liver. In this embodiment, the input purpose is estimated by using “distance measurement” and “area measurement” which are “measurement items” input by the operator using the input device 20 before measurement together with “preliminary information”. It may be the case. That is, this embodiment may be a case where “measurement item” is used as “preliminary information”.

  Then, the determination unit 172 selects a correction mode that is an algorithm for determining a correction point according to the estimated input purpose. 13 and 14 are diagrams illustrating an example of processing of the estimation unit and the determination unit according to the second embodiment.

  For example, as shown in FIG. 13A, it is assumed that the region 60 and the region 61 are designated by the operator's finger on the wall of the lumen. For example, the acquisition unit 171 acquires the position of the center of gravity of the area 60 as the position of the designated point, and acquires the position of the center of gravity of the area 61 as the position of the designated point.

  FIG. 13B shows a profile of the luminance value of the lumen in a line connecting two specified points. In the profile shown in FIG. 13B, each of the peak having the point 62 as a vertex and the peak having the point 63 as a vertex corresponds to the wall of the lumen, and the peak having the point 62 as a vertex and the point 63 as the vertex. The portion sandwiched between the ridges corresponds to the lumen. That is, the portion sandwiched between the points 64 and 65 shown in FIG. 13B corresponds to the inside of the lumen. Here, the point 64 is a point located at the foot of the mountain having the point 62 as a vertex, and the point 65 is a point located at the foot of the mountain having the point 63 as a vertex.

  Here, when measuring the distance of a blood vessel that is a lumen, IMT (Intima Media Thickness) is usually measured. In such a case, the correct answer point of the region 60 is the point 64, and the correct answer point of the region 61 is the point 65. On the other hand, generally, when distance measurement is performed in a lumen such as a breast duct or a hepatic duct, the correct point of the region 60 is the point 62 and the correct point of the region 61 is the point 63.

  However, the region 60 may include both the points 62 and 64, and the region 61 may include both the points 63 and 65. Therefore, the determination unit 172 uses, as a correction point, a point at which the luminance value is an extreme value in a profile in a predetermined direction (for example, the direction of a line segment connecting two specified points) of the luminance value of the pixels constituting the input vicinity area. It is selected according to the input purpose whether to use or a point where the luminance value is substantially constant in the vicinity of the point where the luminance value is an extreme value. Hereinafter, the former determination algorithm is referred to as a first algorithm, and the latter determination algorithm is referred to as a second algorithm. The first algorithm and the second algorithm using the luminance value distribution are algorithms obtained by changing the algorithm of the first determination method described in the first embodiment in accordance with the input purpose. That is, each of the first algorithm and the second algorithm is one of a plurality of correction modes stored in the information storage unit 183, and the determination unit 172 sets the first algorithm or the second algorithm as the correction mode according to the input purpose. 2 Select an algorithm.

  If the estimation result of the estimation unit 174 is “measurement relating to the mammary gland”, the determination unit 172 sets the determination algorithm when distance measurement is performed as the first algorithm. Then, when the positions of the two designated points are output or when the “distance measurement” button is pressed, the determination unit 172 includes the designated points of the region 60 as illustrated in FIG. The correction point is determined as a point 62 from the luminance profile of the input vicinity area, and the correction point is determined as a point 63 from the luminance profile of the input vicinity area including the designated point of the region 61.

  On the other hand, when the estimation result of the estimation unit 174 is “measurement related to blood vessels”, the determination unit 172 sets the determination algorithm when distance measurement is performed as the second algorithm. Then, when the positions of the two designated points are output, or when the “distance measurement” button is pressed, the determination unit 172 includes the designated points of the region 60 as shown in FIG. The correction point is determined as a point 64 from the luminance profile of the input vicinity area, and the correction point is determined as a point 65 from the luminance profile of the input vicinity area including the designated point of the region 61.

  The determination unit 172 may be a case where an algorithm obtained by changing the algorithm of the second determination method described in the first embodiment according to the input purpose is used. FIG. 13C shows a profile of the differential value of the luminance value of the lumen along the line connecting the two designated points. Also in the profile shown in FIG. 13C, each of the peak having the point 62 as the apex and the peak having the point 63 as the apex corresponds to the wall of the lumen, and the portion sandwiched between the points 64 and 65 is the tube. Corresponds to the cavity. Here, as shown in FIG. 13C, the point 62 and the point 63 are extreme values in the differential value profile in the predetermined direction of the differential value of the luminance value of the pixels constituting the input vicinity area. Is a point. Further, as shown in FIG. 13C, the points 64 and 65 are points where the differential values are extreme values in the differential value profile in the predetermined direction of the differential values of the luminance values of the pixels constituting the input vicinity area. The differential value is substantially constant in the vicinity of.

  Therefore, the determination unit 172 uses, as a correction point, a point where the differential value becomes an extreme value in the differential value profile, or the differential value becomes substantially constant in the vicinity of the point where the differential value becomes the extreme value. Whether to use a point as a correction point is selected according to the purpose. When the former is the third algorithm and the latter is the fourth algorithm, when the estimation result of the estimation unit 174 is “measurement relating to the mammary gland”, the determination unit 172 selects the third algorithm. When the estimation result of the estimation unit 174 is “measurement related to blood vessels”, the determination unit 172 selects the fourth algorithm. That is, each of the third algorithm and the fourth algorithm is one of a plurality of correction modes stored in the information storage unit 183, and the determination unit 172 sets the third algorithm or the second algorithm as the correction mode according to the input purpose. Select 4 algorithms.

  Note that the determination algorithm selection processing of the determination unit 172 is also executed in area measurement. For example, when “preset” is “heart”, the estimation unit 174 estimates in advance that the operator inputs a designated point in order to perform measurement related to the heart. Then, when the operator roughly traces the left ventricle depicted in the ultrasound image with a finger and presses the “measure ejection rate” button, the determination unit 172 determines the outer myocardium or the heart wall. Instead, a set of correction points that are points corresponding to the myocardium is determined as a correction curve. Alternatively, if the operator roughly traces the left ventricle depicted in the ultrasound image with a finger and then presses the “measure myocardial volume” button, a correction curve that is a set of correction points corresponding to the epicardium And a correction curve that is a set of correction points corresponding to the myocardium. Such a correction mode is also stored in the information storage unit 183.

  Next, a procedure of processing performed by the ultrasonic diagnostic apparatus 1 according to the second embodiment will be described with reference to FIG. FIG. 15 is a flowchart illustrating a processing procedure performed by the ultrasonic diagnostic apparatus according to the second embodiment.

  As illustrated in FIG. 15, the control unit 170 of the ultrasonic diagnostic apparatus 1 determines whether or not prior information has been input (step S <b> 201). Here, when prior information is not input (No at Step S201), the control unit 170 waits until prior information is input.

  On the other hand, when prior information is input (Yes at Step S201), the estimation unit 174 estimates a purpose (input purpose) from the prior information (Step S202). And the control part 170 determines whether the ultrasonic image was displayed and the measurement start instruction | indication was input (step S203). Here, when a measurement start instruction is not input (No at Step S203), the control unit 170 stands by until a measurement start instruction is input.

  On the other hand, when a measurement start instruction is input (Yes at Step S203), the determination unit 172 selects a determination algorithm according to the input purpose (Step S204), and the acquisition unit 171 receives an input of a specified point from the operator. It is determined whether or not (step S205). Here, when the input of the designated point is not accepted (No at Step S205), the control unit 170 waits until the designated point is accepted.

  On the other hand, when the input of the designated point is received (Yes at Step S205), the acquisition unit 171 obtains the position of the designated point (Step S206). Then, the determination unit 172 sets an input neighborhood area from the position of the designated point (step S207).

  Then, the determination unit 172 corrects the position of the designated point based on the image information of the input vicinity area and the selected determination algorithm, and determines the correction point (step S208). Then, the monitor 30 displays the correction point (step S209) and ends the process. Although not shown, measurement processing of the measurement unit 173 is performed after step S209. Note that the monitor 30 may be configured to display the designated point and the correction point at the same time after changing the color, for example, when the positions of the designated point and the correction point are different under the control of the control unit 170. .

  As described above, in the second embodiment, in order to cope with the change of the optimal algorithm according to the measurement purpose, input of a diagnosis region or the like is performed using prior information normally input in an ultrasonic examination workflow. Estimate the purpose. In the second embodiment, an optimal algorithm is selected based on the estimated purpose. Thereby, in the second embodiment, it is possible to determine a correction point that matches the operator's request without the operator inputting special information.

(Third embodiment)
In the third embodiment, a case where information to be input target estimation target is acquired from an ultrasound image will be described with reference to FIG. FIG. 16 is a diagram for explaining the third embodiment.

  An ultrasonic diagnostic apparatus 3 according to the third embodiment will be described. Since the configuration of the ultrasonic diagnostic apparatus 3 according to the third embodiment is substantially the same as the configuration of the ultrasonic diagnostic apparatus 1 illustrated in FIG. 1, illustration thereof is omitted. The configuration of the control unit 170 according to the third embodiment is substantially the same as the configuration of the control unit 170 according to the second embodiment illustrated in FIG. However, the estimation unit 174 of the control unit 170 according to the third embodiment performs the following estimation process. That is, the estimation unit 174 according to the third embodiment estimates a diagnostic site depicted in the ultrasound image as one of input purposes based on the feature amount of the ultrasound image.

  That is, the estimation unit 174 according to the third embodiment estimates the input purpose by “scene recognition” using the currently displayed ultrasonic image. There are organ-specific patterns in the organs depicted in each diagnosis region. Therefore, for example, “an ultrasonic image in which a characteristic pattern of each organ is depicted” is stored in the storage unit 180. The estimation unit 174 compares the currently displayed ultrasound image with the ultrasound images of various organs stored in the storage unit 180, thereby estimating the organ depicted in the display image, thereby making a diagnosis. The part is estimated.

  Alternatively, for example, “a feature amount of an ultrasonic image in which a characteristic pattern of each organ is depicted” is stored in the storage unit 180. The estimation unit 174 extracts the feature amount of the currently displayed ultrasonic image. Then, the estimation unit 174 compares the extracted feature quantity with the feature quantities of various organs stored in the storage unit 180, thereby estimating the organ depicted in the display image, thereby estimating the diagnosis part. To do. For example, as illustrated in FIG. 16, the estimation unit 174 estimates that the organ depicted in the display image is the liver, and outputs “diagnosis site: liver”.

  The diagnosis part estimated by such processing is notified to the determination unit 172, as in the prior information described in the second embodiment, and the determination unit 172 selects a determination algorithm. For example, since the determination unit 172 is “diagnosis site: liver”, when distance measurement is performed, the determination unit 172 selects the first algorithm or the second algorithm.

  As described above, in the third embodiment, since the diagnosis site is estimated from the ultrasound image, it is possible to improve the estimation accuracy of the input purpose.

  In the first to third embodiments described above, the case where the size of the input vicinity area is fixed has been described. However, in the first to third embodiments described above, the size of the input vicinity area may be changed according to the input purpose. FIG. 17 is a diagram for explaining a modification of the input vicinity area.

  That is, the determination unit 172 changes the “predetermined range” for setting the size of the input vicinity area according to the input purpose. For example, as shown in FIG. 17, it is assumed that the operator presses the “Area measurement” button even though only the position of one point 66 is acquired as the designated point. In such a case, the determination unit 172 changes the input vicinity area of “9 pixels × 9 pixels” with the point 66 as the center. For example, the determination unit 172 changes to an ellipse 67 centered on the point 66 as shown in FIG. Here, the determination unit 172 sets the lengths of the long axis and the short axis so that the size of the ellipse is 1/500 of the image size, and sets the ellipse 67 as the input neighborhood area. And the determination part 172 determines a correction curve by the process demonstrated using FIG. 8, for example. The correction mode that defines the determination method described using FIG. 17 is also stored in the information storage unit 183.

  In such a modification, the operator automatically obtains a trace result of a curve for area measurement only by performing an input operation for specifying one point and an input operation for pressing an “area measurement” button, for example. be able to. According to this modification, it is possible to further facilitate an input operation on the ultrasonic image.

  In the first to third embodiments and the modifications described above, the case where the correction point is determined using the pixel value (luminance value) of the B-mode image has been described. However, in the above-described first to third embodiments and modifications, the values (measurement values) assigned to the pixels of the ultrasound image other than the B-mode image generated by the ultrasound diagnostic apparatus are used. The correction point may be determined. For example, the determination unit 172 distributes “velocity value”, “power value”, “dispersion value” assigned to each pixel in the color Doppler image, or “velocity value”, “power value”, “dispersion value”. Alternatively, the correction point may be determined based on the spatial differentiation. Alternatively, for example, the determination unit 172 may determine a correction point based on the distribution of the “strain value” assigned to each pixel in the strain image or the spatial differentiation of the “strain value”. Alternatively, for example, the determination unit 172 may determine a correction point based on a distribution of “distortion values” assigned to each pixel in an elastography image or a spatial differentiation of “distortion values”.

  In the first to third embodiments and the modifications described above, image processing for facilitating an input operation on an ultrasound image is performed in the ultrasound diagnostic apparatus that is a medical image diagnostic apparatus. Explained. However, the above-described image processing may be performed on a medical image in a medical image diagnostic apparatus such as an X-ray CT apparatus or an MRI apparatus.

  Further, the image processing described above may be executed by an image processing apparatus installed independently of the medical image diagnostic apparatus. Specifically, an image processing apparatus having a function such as the control unit 170 shown in FIG. 2 or FIG. 11 uses a PACS (Picture Archiving and Communication Systems) database, which is a system for managing various types of medical image data, There may be a case where medical image data is received from a database or the like of an electronic medical chart system that manages an electronic medical chart to which an image is attached, and the above-described image processing is performed.

  Further, each component of each illustrated apparatus is functionally conceptual, and does not necessarily need to be physically configured as illustrated. In other words, the specific form of distribution / integration of each device is not limited to that shown in the figure, and all or a part thereof may be functionally or physically distributed or arbitrarily distributed in arbitrary units according to various loads or usage conditions. Can be integrated and configured. Further, all or any part of each processing function performed in each device may be realized by a CPU and a program analyzed and executed by the CPU, or may be realized as hardware by wired logic.

  The image processing method described in the present embodiment can be realized by executing an image processing program prepared in advance on a computer such as a personal computer or a workstation. This program can be distributed via a network such as the Internet. The image processing program can also be executed by being recorded on a computer-readable recording medium such as a hard disk, a flexible disk (FD), a CD-ROM, an MO, or a DVD, and being read from the recording medium by the computer. .

  As described above, according to the first to third embodiments and the modification examples, it is possible to facilitate an input operation on a medical image.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the spirit of the invention. These embodiments and their modifications are included in the scope and gist of the invention, and are also included in the invention described in the claims and the equivalents thereof.

DESCRIPTION OF SYMBOLS 1 Ultrasonic diagnostic apparatus 10 Ultrasonic probe 20 Input apparatus 30 Monitor 100 Apparatus main body 110 Transmission part 120 Reception part 131 B mode processing part 132 Doppler processing part 140 Image generation part 150 Image memory 160 Image composition part 170 Control part 171 Acquisition part 172 Determination unit 173 Measurement unit 180 Storage unit 190 Interface unit

Claims (13)

An input unit that accepts designation of measurement items using medical images;
An acquisition unit for acquiring a position of the designated point designated on the medical image by the operator in the medical image;
A storage unit for storing a plurality of correction modes for correcting the position of the designated point based on image information of a neighboring region within a predetermined range from the position of the designated point including the designated point in the medical image;
A determination unit that corrects the position of the designated point according to a predetermined correction mode determined based on the measurement item, and determines the point of the corrected position as a correction point;
A measurement unit that performs measurement based on the position of the correction point and the measurement item;
An image processing apparatus comprising: An acquisition unit for acquiring a position of the designated point designated on the medical image by the operator in the medical image;
A storage unit for storing a plurality of correction modes for correcting the position of the designated point based on image information of a neighboring region within a predetermined range from the position of the designated point including the designated point in the medical image;
A determination unit that selects one correction mode from among the plurality of correction modes, corrects the position of the designated point, and determines the point of the corrected position as a correction point;
An image processing apparatus comprising:   At least one of the plurality of correction modes stored in the storage unit is a correction mode in which the correction point is determined based on a distribution of luminance values of pixels constituting the neighboring area. Item 3. The image processing apparatus according to Item 1 or 2.   At least one of the plurality of correction modes stored in the storage unit is a correction mode in which the correction point is determined based on a spatial differentiation of luminance values of pixels constituting the neighboring area. The image processing apparatus according to claim 1.   The said determination part further changes the correction mode used for determination of the said correction point according to the objective in which the said operator input the said designated point, The change to any one of Claims 1-4 characterized by the above-mentioned. The image processing apparatus described. At least one of the plurality of correction modes stored in the storage unit is:
In the profile in the predetermined direction of the luminance value of the pixels constituting the neighboring region, the correction mode using a point where the luminance value becomes an extreme value as the correction point,
At least one of the plurality of correction modes stored in the storage unit is:
The correction mode uses a point at which the luminance value is substantially constant in the vicinity of a point where the luminance value is an extreme value in the profile in a predetermined direction of the luminance value of the pixels constituting the neighboring region as the correction point. The image processing apparatus according to claim 5. At least one of the plurality of correction modes stored in the storage unit is:
In the profile in the predetermined direction of the differential value of the luminance value of the pixels constituting the neighboring region, the correction mode using the point where the differential value becomes an extreme value as the correction point,
At least one of the plurality of correction modes stored in the storage unit is:
In a correction mode in which a point at which the differential value is substantially constant in the vicinity of a point where the differential value is an extreme value in the profile in a predetermined direction of the luminance value of the pixels constituting the vicinity region is used as the correction point. The image processing apparatus according to claim 5, wherein the image processing apparatus is provided. An estimation unit that estimates the purpose of the operator inputting the designated point based on prior information regarding the medical image that is input before the designated point is input;
Further comprising
The image processing apparatus according to claim 5, wherein the determination unit further changes a correction mode used for determination of the correction point in accordance with the purpose estimated by the estimation unit.   The image processing apparatus according to claim 8, wherein the estimation unit estimates, as one of the purposes, a diagnostic part drawn on the medical image based on a feature amount of the medical image.   The image processing apparatus according to claim 5, wherein the determination unit changes the predetermined range according to the purpose.   The image processing apparatus according to claim 1, wherein the designated point is designated by a finger input on the touch panel of the operator. An ultrasonic probe that transmits ultrasonic waves and receives reflected waves of the transmitted ultrasonic waves; and
An image generator for generating an ultrasonic image from the reflected wave;
An input unit that accepts designation of a measurement item using the ultrasonic image;
An acquisition unit for acquiring a position of the designated point designated on the ultrasonic image by the operator in the ultrasonic image;
A storage unit that stores a plurality of correction modes for correcting the position of the designated point based on image information of a neighboring region that is within a predetermined range from the position of the designated point, including the designated point in the ultrasonic image;
A determination unit that corrects the position of the designated point according to a predetermined correction mode determined based on the measurement item, and determines the point of the corrected position as a correction point;
A measurement unit that performs measurement based on the position of the correction point and the measurement item;
An ultrasonic diagnostic apparatus comprising: An input procedure for accepting specification of measurement items using medical images;
An acquisition procedure for acquiring a position of the designated point designated on the medical image by the operator in the medical image;
Refer to a storage unit that stores a plurality of correction modes for correcting the position of the designated point based on image information of a neighboring region that is within a predetermined range from the position of the designated point including the designated point in the medical image. A determination procedure for correcting the position of the designated point according to a predetermined correction mode determined based on the measurement item, and determining the point of the corrected position as a correction point;
A measurement procedure for performing measurement based on the position of the correction point and the measurement item;
An image processing program for causing a computer to execute.

Images