JPH064075B2 - Ultrasonic diagnostic equipment - Google Patents

Description

Description: (a) Technical Field of the Invention The present invention relates to an ultrasonic diagnostic apparatus, and more particularly to a display method of a Doppler sample position mark in an M mode image when a Doppler sample position is set.

(b) Background of technology Normally, when Doppler measurement is performed with an ultrasonic diagnostic apparatus, first, B
It is controlled to set a Doppler sample position on the mode image and display the M mode image and the Doppler mode image for the Doppler sample position.

In order to set the Doppler sample position on the B-mode image, it is necessary to determine the position where the Doppler measurement is performed in the entire B-mode image of the target organ of the subject.

When an M-mode image at the Doppler sample position determined in the above process is displayed with a display length determined by the display mode, etc., a detailed M-mode image cannot be obtained, so only the vicinity of the Doppler sample position is enlarged. M
It is necessary to display the mode image.

On the other hand, in the Doppler measurement, the measurement result is recorded on a recording paper, but there is a demand to reduce the width of the recording paper from the viewpoint of operating cost. When an M-mode image is to be recorded, the M-mode image is magnified only in the vicinity of the Doppler sample position (that is, the display start point of the M-mode image is shifted according to the sample position and magnified). There is a need to.

From these things, when performing Doppler measurement, there has been a demand for an effective display method of the M-mode image in which only the periphery of the sample position is enlarged corresponding to the Doppler sample position.

(c) Conventional technology and problems B in which an entire target organ is displayed in an ultrasonic diagnostic apparatus having a function of setting a Doppler sample position on a B-mode image and displaying the M-mode image according to the sample position. When a Doppler sample position is set on the mode image, an M mode image having a display length determined by the display mode is displayed for the set sample position, and then the display magnification of the M mode image is changed,
The sample position may extend out of the display area of the M mode. In this case, in the conventional method,
The sample position was automatically moved into the M-mode image.

However, when performing Doppler measurement, since the absolute position of the Doppler sample position from the body surface of the subject is important, the sample position can be changed by changing the display magnification of the M-mode image as described above. When automatically moved, there is a problem that it is necessary to manually shift the display start point of the M mode and set the sample position again on the B mode image.

(d) Object of the Invention In view of the above-mentioned conventional drawbacks, the present invention provides an ultrasonic diagnostic apparatus having a Doppler measurement function, in which a Doppler sample position is set on a B-mode image, an M-mode image is displayed, and then the M-mode When the display magnification of the image is increased, the displayable area of the M mode is automatically adjusted so that the displayable area becomes smaller, the depth from the body surface becomes shallower, and the sample position does not protrude from the display area of the M mode. The purpose is to provide a method of lowering it.

(e) Structure of the Invention According to the present invention, there is provided a means for setting a Doppler sample position on a B-mode image, a means for displaying the M-mode image according to the set Doppler sample position, and a means for displaying the M-mode image. An ultrasonic diagnostic apparatus having means for changing a display magnification (scale factor) n, wherein the distance (unit: centimeters, etc., hereinafter) from the B mode display origin to the M mode display start point is a, The distance from the B-mode display origin to the M-mode display end point is b, the distance from the B-mode display origin to the Doppler sample position on the M bright line is d, and the number of pixels in the M-mode display area is l. When the mode display magnification (scale factor) is n, the distance a from the B mode display origin to the M mode display start point is controlled under the condition of a ≦ d ≦ a + nl. Means for changing the display magnification (scale factor) n in the M mode to display the M mode image, the distance a from the B mode display origin to the M mode display start point is controlled by the control means. Achieved by providing a device for controlling and always displaying Doppler sample position marks in the M-mode image,
Even if the display magnification of the mode is increased, there is an advantage that the Doppler sample position mark on the M mode image can always be displayed on the M mode image.

(f) Embodiment of the Invention First, in summary of the gist of the present invention, the present invention provides an ultrasonic wave having a function of setting a Doppler sample position on a B-mode image and displaying an M-mode image according to the Doppler sample position. In the diagnostic device, when an M-mode image having a display length determined by the display mode is displayed and then the display magnification of the M-mode is enlarged, the display start point of the M-mode is lowered in accordance with the display magnification. The Doppler sample position mark is always displayed in the mode image.

Embodiments of the present invention will be described in detail below with reference to the drawings. FIG. 1 is a diagram for explaining the concept of the present invention, and FIG. 2 is a block diagram showing an embodiment of the present invention.

In FIG. 1, 1 is the display area of the B mode image, 2 is the M mode display length on the M bright line, 3 is the Doppler sample position, a is the distance from the B mode display origin to the M mode display start point, and b is B. The distance from the mode display origin to the M mode display end point, d is the distance from the B mode display origin to the Doppler sample position on the M bright line, l and nl are the number of pixels in the M mode display area, generally depending on the image memory capacity. It is usually about 400 pixels.

Now, in order to perform the Doppler measurement, the B-mode image 1 for a specific organ is displayed, the Doppler sample position 3 for performing the Doppler measurement is set on the B-mode image 1, and the display length (b It is assumed that the M-mode image of -a) is displayed.

At this time, the Doppler sample position mark is displayed in the M mode image as shown.

When the display magnification of the M mode is enlarged in this state, the display area of the M mode is reduced (that is, b in the figure is shortened) corresponding to the magnification, and the Doppler sample position 3 gives an instruction. The Doppler sample position mark may run off the M-mode image.

Therefore, in order to control so that the Doppler sample position 3 does not protrude from the M mode image even if the display magnification in the M mode is increased, the relationship of a ≦ d ≦ b ... However, it is necessary to increase the value of a indicating the starting point of M mode display.

However, if the display magnification in the M mode (that is, scale factor = display length per pixel) is n, then b−a = nl (l: number of pixels). That is, the display magnification n is represented by (ba) / l,
The dimension is, for example, centimeters / pixel, and the number of pixels in the M-mode display area, for example, 40 pixels described above.
The 0 pixel represents the human body length per pixel when the M mode display length of the human body on the M bright line is displayed.

For example, as the initial display magnification, a portion of ba = 5 cm was displayed with l = 400 pixels {that is, n-5 / 400 cm / pixel at this time) in the same display area. If you try to display the 2.5 cm portion, it will be enlarged.

The display magnification (scale factor) n at that time is 1/2 times the initial value, and in general, when enlarged display is performed, the value of the display magnification (scale factor) n becomes small.

From the equation of b−a = nl, b = a + nl, and when the display magnification of the M mode is determined in the enlargement direction, nl becomes a fixed value smaller than the initial value, so the above inequality is a ≦ d ≦ a + nl ........ When enlarged, the display magnification (scale factor) n becomes smaller and the value of nl becomes smaller as described above. Therefore, while satisfying the condition of the above equation, By increasing the size, the Doppler sample position 3 can always be included in the enlarged M mode image.

The main object of the present invention is a control method in which the value of a is increased within the range of the above conditions in correspondence with the display magnification n in the M mode.

FIG. 2 is a block diagram showing the specific control method.
Particularly, the portion surrounded by the dotted line is the functional block related to the present invention.

In FIG. 2, 4 is an M mode display magnification (scale factor: indicates one pixel length of an M mode image when the magnification is n) designating unit (Mn), 5 is a joystick, 6 is a Doppler position counter (DPCOT), 7 Is the M mode start point counter (MSCOT)
At the time of displaying the M mode image, the operation panel (not shown)
Enter the initial value from. An M-mode display length register (MLR) 8 is set with a value determined by the display mode of the ultrasonic diagnostic apparatus or an input value from the operation panel. A comparator (COP) 9 is controlled to perform the above-mentioned comparison operation, calculate a satisfying the condition of, and feed back to the M-mode start point counter (MSCOT) 7. 10 is a multiplier and 11 is an adder.

First, as shown in FIG. 1, it is assumed that the Doppler sample position 3 is set on the B mode image 1 and the M mode image given by the M mode display length 2 is displayed.

At this stage, when the M mode display magnification designating key on the operation panel is pressed, the scale factor n corresponding to the designated magnification is multiplied by the multiplier from the M mode display magnification designating unit (Mn) 4.
Entered in 10.

Next, when the Doppler sample position mark 3 displayed on the B-mode image is moved to a predetermined position by the joystick 5 on the operation panel, the Doppler position counter corresponds to the moving direction (up / down). (DPCOT)
When 6 counts up / down and reaches a predetermined position, a numerical value indicating the position is output, and the multiplier 10 outputs n
Is multiplied by and the value d indicating the position of the Doppler sample position is determined and input to the comparison decision (COP) 9.

In the same way, the M mode start point counter (MSCO
The M mode display start point position a indicated by the initial value input to (T) is determined, and this M mode start point counter (MSCOT)
The value of 7 and the value of the M mode display length register (MLR) 8 are added by the adder 11 to determine the M mode end point position b, which are input to the comparator (COP) 9.

In the comparator (COP) 9, the comparison operation shown in (1) is performed, the value of a that satisfies the condition shown in (3) is calculated, and the feedback amount corresponding to the value is fed back to the M-mode start point counter (MSCOT) 7. Works like.

Corresponding to the above feedback amount, M mode start point counter (MSCO
The value of T) 7 is counted up / down and updated to the M mode display start position where the Doppler sample position mark does not protrude from the M mode image.

As a result, the M-mode image is displayed as a M-mode image having a predetermined display length from the updated display start point and always including the Doppler sample position mark therein, and the object of the present invention is achieved. Will be.

(g) Effects of the Invention As described above in detail, the ultrasonic diagnostic apparatus of the present invention sets the Doppler sample position on the B-mode image,
When the M mode image is displayed according to the set Doppler sample position, the distance from the B mode display origin to the M mode display start point is a
The distance from the B mode display origin to the M mode display end point is b, the distance from the B mode display origin to the Doppler sample position on the M bright line is d, and the number of pixels in the M mode display area is 1. When the M mode display magnification (scale factor) is n, a means for controlling the distance a from the B mode display origin to the M mode display start point is provided under the condition of a ≦ d ≦ a + nl. When the display magnification (scale factor) n of the mode is changed to display the M-mode image, the control means controls the distance a from the B-mode display origin to the M-mode display start point to obtain the M-mode. Since the Doppler sample position mark is always displayed in the image, the distance d from the display origin of the B mode image to the Doppler sample position does not change. In a limited M mode display regions (i.e., M-mode display length) in includes the Doppler sample position mark, the effect of and it is possible to obtain an enlarged detail M-mode image.

[Brief description of drawings]

FIG. 1 is a diagram for explaining the concept of the present invention, and FIG. 2 is a block diagram showing an embodiment of the present invention. In the drawing, 1 is the display area of the B mode image, 2 is the M mode display length, 3 is the Doppler sample position, a is the distance from the B mode display origin to the M mode display start point, and b is the B mode display origin to the M mode. Distance to display end point, d is B
The distance from the mode display origin to the Doppler sample position on the M bright line, l is the number of pixels in the M mode display area, 4 is the M mode display magnification designating section (Mn), 5 is the joystick, and 6
Is Doppler position counter (DPCOT), 7 is M mode start point counter (MSCOT), 8 is M mode display length register (ML
R) and 9 are comparators (COPs), 10 is a multiplier, and 11 is an adder.

Claims (1)

[Claims] 1. A means for setting a Doppler sample position on a B-mode image and displaying an M-mode image according to the set Doppler sample position, and a means for changing a display magnification (scale factor) n of the M-mode image. An ultrasonic diagnostic apparatus having: a, a distance (unit: centimeters, etc.) from the B mode display origin to the M mode display start point is a, and a distance from the B mode display origin to the M mode display end point is b When the distance from the B mode display origin to the Doppler sample position on the M bright line is d, the number of pixels in the M mode display area is 1, and the M mode display magnification (scale factor) is n, a ≦ Under the condition of d ≦ a + nl, means for controlling the distance a from the B mode display origin to the M mode display start point is provided, and the display magnification (scan rate of the M mode When an M mode image is displayed by changing the Kale factor) n, the control means controls the distance a from the B mode display origin to the M mode display start point so that the Doppler sample is always displayed in the M mode image. An ultrasonic diagnostic apparatus characterized by displaying a position mark.