Ultrasonic color doppler diagnostic apparatus

Abstract: An ultrasonic color Doppler diagnostic apparatus for displaying at least two successive frames of original images of the two-dimensional images obtained for each ultrasonic interframe time, to find and display a natural interpolated image, it comprises a shape parameter calculating unit (110) which calculates the shape parameters characterizing the shape of a blood flow region on the original images, a shape parameter interpolating unit (112) which calculates the shape parameters interpolated at a designated timing designated in the interframe time from the said shape parameters, the interframe time, and the designated timing, an image converting unit (113) which converts the image of at least one frame of the original image in the plurality of original images in accordance with the shape parameters at a designated timing found by the shape parameter interpolating means to obtain the interpolated image, and a displaying means (116) which displays a moving image comprised of the interpolated images inserted in between the original images and moving images of only the interpolated images.

Description: The present invention relates to an ultrasonic color Doppler diagnostic apparatus which performs image interpolation so as to improve the ultrasonic frame rate in appearance. In recent years, the importance of obtaining a grasp of the state of blood behaviour in heart disease and the carotid arteries has been rising in the field of clinical diagnosis. Presented here is an ultrasonic color Doppler diagnostic apparatus which can display color images of the state of blood behavior safely and simply in real time. Conventional ultrasonic color Doppler diagnostic apparatuses display in real time a combination of the B mode image of the muscle of the heart or other organ in the specimen and the average speed, speed dispersion, or Doppler signal power of the blood flowing through a specimen (hereinafter referred to as blood flow speed data). This enabled observation of the flow of blood in the organs and was extremely convenient in obtaining a grasp of the state of the blood behaviour the organs. As described in more detail later with reference to the drawings, ideally, for example, while it is desired to see the blood flow changing slowly and smoothly with each television frame, in practice the image changes in spurts and doctors using the apparatus feel the movement of the heart and changes in the state of the blood flow are awkward, and therefore cannot make an adequate diagnosis. The following three methods were considered in the prior art to overcome this problem: The first conventional method was to change the control of the beam former so as to reduce the number of ultrasonic pulses sent and received in the same direction of the specimen by changing the direction of sending and receiving signals in rough angles, or else the range of angles of signal transmission and reception was made narrower so as to substantially improve the ultrasonic frame rate. In this first method, however, the flow rate data obtained could only be obtained at rough positions in two dimensions, or else the flow rate data could only be obtained in a narrow range of angles. As a result, there was undeniably a deterioration of the quality of the flow image as compared with the usual display. In a second conventional method, simultaneous multidirectional signal transmission and reception was used so as to obtain signals received from a plurality of directions. In this second conventional method, a plurality of beam formers is necessary, so inevitably the cost becomes higher and the apparatus becomes larger in size, which is not necessarily satisfactory to the user. The cost reductions made possible by advances in semiconductor technology further cannot be expected to contribute much to beam formers. In a third conventional method, an interpolation and a weighting are employed to obtain an estimated image between two original images. In this third conventional method, it is possible to improve the apparent ultrasonic frame rate simply and inexpensively, but when the position and angle of the blood flow differ greatly among original images, then, a false blood flow completely different from the true images ends up being displayed, with the resulting danger of mistaken diagnosis. It is accordingly desirable to improve upon the above three methods and to provide an apparatus which increases the apparent ultrasonic frame rate without the above defect, that is finds from the images of the natural interpolated images and displays the same. According to the present invention there is provided an ultrasonic color Doppler diagnostic apparatus for displaying at least two successive frames of two-dimensional images obtained in an ultrasonic interframe time, operable to transmit an ultrasonic pulse in a plurality of directions with respect to a subject, process the signal received, and display the results as a two-dimensional image of the average speed, speed dispersion, or Doppler signal power of blood flowing in the subject, comprising: a shape parameter calculating means for calculating the shape parameters characterising the shape of blood flow regions on the original images, a shape parameter interpolating means for calculating shape parameters interpolated at a timing designated in said interframe time from the said shape parameters calculated on the original images, said interframe time, and said designated timing, an image converting means for converting the image of at least one of said frames of original images in accordance with the shape parameters at the designated timing found by said shape parameter interpolating means to obtain interpolated images, and a displaying means for displaying as moving images the interpolated images inserted in between the original images or only the interpolated images. Preferably, the apparatus further comprises a weighted averaging unit for weighting the interpolated images obtained by the image converting unit and for averaging the weighted interpolated images. The weighted averaging unit comprises a first weighting unit for weighting, by a value (t2 - th)/(t2 - t1) , a first interpolated image, where t1 is a first timing corresponding to a first frame original image, t2 is a second timing corresponding to a second frame original image, and th is the designated timing, the first interpolated image being obtained by converting, by the image converting means, the first frame original image; a second weighting unit for weighting a second interpolated image by the value (t2 - th)/(t2 - t1) , where the second interpolated image being obtained by converting, by the image converting means, the second frame original image; and an adding unit for adding the weighted first and second interpolated images. The shape parameter interpolating unit may be a shape parameter linear interpolating means for performing linear interpolation on the shape parameters of a second frame original image in accordance with the interframe time and the designated timing and thereby calculates interpolated shape parameters. Alternatively, the shape parameter interpolating unit may be a shape parameter high order interpolating unit for calculating any function passing through the shape parameters of at least three frames of original images, then for calculating the interpolated shape parameters at the designated timing as values of the function at the designated timing. Desirably, the apparatus further comprises a shape parameter averaging means for averaging a plurality of frames worth of shape parameters for each frame calculated in the shape parameter calculating means. Preferably, the apparatus further comprises a characteristic judgment unit for judging the characteristic of the average speed, speed dispersion, or Doppler signal power of the blood flowing in a subject at pixels of the original image; and an image dividing means which divides into a plurality of images the original image in accordance with the characteristic of the average speed, speed dispersion, or Doppler signal power of the blood flowing in the subject; the divided images obtained by the division being deemed as original images and used to find the interpolated images. The characteristic judging unit may be a sign judging unit for performing judgment of the sign of the average speed. Alternatively, the characteristic judging unit may be a mosaic pattern judging unit for judging that the number of the pixels having an average speed of over a predetermined speed +Vth and the number of pixels having an average speed less than a predetermined speed -Vth, in the pixels surrounding and including a particularly noted pixel together are more than a predetermined number so that the pattern is a mosaic one. The characteristic judging unit may instead be a labelling means for applying the same label to pixels constituting connecting portions for each connecting portion where pixels adjoin and form a single cluster. In an embodiment of the present invention, the apparatus further comprises a blood flow region presence judging unit for judging if there is a region in which blood is flowing in at least one original image in the two frames; and an image interpolation bypassing unit which bypasses the said image converting unit in accordance with the results of the above detection and thereby directly inputs the original image in the weighted averaging means. In another embodiment of the present invention, the displaying unit has a display suppressing unit which suppresses the display of pixels outside of the range of measurement of the average speed, speed dispersion, or Doppler signal power of blood flowing in a subject. In a further embodiment, the displaying unit may comprise an interpolated image synthesizing unit which displays, among the pixels of the interpolated images obtained from the plurality of divided images, the ones with the maximum absolute values of the average speed of the blood flow. In yet another embodiment of the present invention, a two-dimensional image of the average speed, speed dispersion, or Doppler signal power of the blood flowing through a subject is used as the original image and at the same time use is made of a B mode image as an original image to produce and display an interpolated image of the B mode image. In a still further embodiment of the present invention, the apparatus further comprises: an image separating unit for separating a B mode image and a two-dimensional image of the average speed, speed dispersion, and Doppler signal power of the blood flowing in the specimen from an NTSC, RGB, or other image signal; and a flow rate data normalizing unit for normalizing the pixel value of the two-dimensional image of the average speed, speed dispersion, or Doppler signal power of blood flowing in a specimen, using a pixel value of a color bar showing the correspondence between the average speed, speed dispersion, or Doppler signal dispersion of blood flowing in a specimen and color. In yet another embodiment of the present invention, the apparatus further comprises: an original image frame memory for three or more frames, an original image selecting unit for selecting two frames of original images from the original image frame memory, an interpolated image frame memory for storing interpolated images, and a displayed frame selecting unit for selecting any one frame in the original image frame memory and interpolated image frame memory, the interpolated image being displayed at the time of reproduction of a cine loop. The above described apparatus may further comprise a display format for notifying at the time of cine loop reproduction or freezing if the displayed image is an original image or an interpolated image. In the above described apparatus, a frame to be frozen at the time of reproduction of the cine loop may be specified as an original image frame. Reference will now be made, by way of example, to the accompanying drawings, in which:- Figure 1 is an explanatory view of the present invention; Figure 2 is a constitutional view of a first embodiment of the present invention; Figures 3A to 3G, Figs. 4A and 4B, Figs. 5A to 5C, and Fig. 6 are views for use in explaining the principle of the first embodiment; Figure 7 is a constitutional view of a second embodiment of the present invention; Figure 8 is a constitutional view of a third embodiment of the present invention; Figure 9 is a view for use in explaining the principle of the third embodiment; Figure 10 is a constitutional view of a fourth embodiment of the present invention; Figure 11 is a view for use in explaining the principle of the fourth embodiment; Figure 12 is a constitutional view of a fifth embodiment of the present invention; Figures 13A to 13F are views for use in explaining the principle of the fifth embodiment of the present invention; Figure 14 is a view for use in explaining another example of the constitution of the fifth embodiment; Figure 15 and Fig. 16 are constitutional views of the sixth embodiment of the present invention; Figure 17 and Figs. 18A to 18F are views for use in explaining the principle of the sixth embodiment; Figure 19 is a constitutional view of the seventh embodiment of the present invention; Figures 20A to 20F and Figs. 21A to 21D are views for use in explaining the principle of the seventh embodiment; Figures 21E and 21F is a flowchart for use in explaining the operation of the seventh embodiment; Figure 22 is a constitutional view of the eighth embodiment of the present invention; Figures 23A to 23C are constitutional views of the ninth embodiment of the present invention; Figures 24A and 24B are views for use in explaining the effect of the ninth embodiment; Figure 25 is a constitutional view of the 10th embodiment of the present invention; Figure 26 is a constitutional view of the 11th embodiment of the present invention; Figure 27 is a constitutional view of the 12th embodiment of the present invention; Figure 28 is a view for use in explaining the operation of the 12th embodiment of the present invention; Figure 29 is a constitutional view of the 13th embodiment of the present invention; Figures 30A and 30B are views for use in explaining the display method in the 13th embodiment of the present invention; Figures 31A and 31B are views for use in explaining the control method in the 13th embodiment of the present invention; Figure 32 is a view showing one example of the conventional apparatus; and Figures 33A to 33G, Figs. 34A to 34E, Figs. 35A and 35B, Fig. 36, and Figs. 37A to 37G are views for use in explaining the conventional problems. Figure 32 shows conventional ultrasonic color Doppler diagnostic apparatus, in which 100 is a transmitter for transmitting an ultrasonic wave signal 101 is an ultrasonic probe which sends and receives an ultrasonic wave signal, 102 is a beam former which forms an ultrasonic beam, 103 is a detection circuit which detects the ultrasonic signal output from the beam former 102, 104 is a digital scan converter (DSC) which receives as input the detection signal and outputs B mode image data, 105 is a color Doppler analysis unit which calculates the blood flow speed data from the ultrasonic signal, and 106 is a digital scan converter (DSC) which converts the blood flow speed data to flow image data and outputs the same. Reference numeral 3201 is a displaying unit, which displays the original images, interpolated images, and B mode images. Here, in the conventional apparatus, the blood flow speed data was acquired while sending and receiving a plurality of ultrasonic pulses in the same direction of the specimen, so while the television frame rate was 30 frames, the ultrasonic frame rate was limited to about 10 frames. Therefore, ideally, for example, while it is desired to see the blood flow changing slowly and smoothly with each television frame as in Figs. 33A, 33B, 33C, 33D, 33E, and 33F, in the case of 7.5 ultrasonic frames, there is the problem that the actually displayed image changes in spurts, such as A, A, A, A, E, E as shown in Fig. 33G and the doctor using the apparatus feels the movement of the heart and changes in the state of the blood flow is awkward and therefore cannot make an adequate diagnosis. As mentioned above, three methods were considered in the prior art to overcome this problem. In the first conventional method, the control of the beam former 102 of Fig. 34A was changed so as to reduce the number of ultrasonic pulses sent and received in the same direction of the specimen by changing the direction of sending and receiving signals in rough angles as shown in Fig. 34C, or else the range of angles of signal transmission and reception was made narrower as shown in Fig. 34D so as to substantially improve the ultrasonic frame rate. By this change, the time required for scanning the specimen can be shortened, in comparison with the full scanning shown in Fig. 34B. In this first method, however, the flow rate data obtained could only be obtained at rough positions in two dimensions as shown in Fig. 34C, or else the flow rate data could only be obtained in a narrow range of angles as shown in Fig. 34D. As a result, there was undeniably a deterioration of the quality of the flow image as compared with the usual display as shown in Fig. 34B. In a second conventional method, as illustrated in Fig. 35A, simultaneous multidirectional signal transmission and reception was used so as to obtain signals received from a plurality of directions, as shown by Lr and L1 in Fig. 35B, by a single transmission. By this method, an apparatus was realized which substantially improved the ultrasonic frame rate. In Fig. 35A, 101 is an ultrasonic probe which sends and receives an ultrasonic wave. The output of the ultrasonic probe 101 is connected to two beam formers 102 and 3501. The beam former 102 forms an ultrasonic beam, 103 is a detection circuit which detects an ultrasonic signal output from the beam former 102, 104 is a digital scan converter which receives as input the detection signal and outputs the B mode image data, 105 is a color Doppler analysis unit which calculates the blood flow speed data from the ultrasonic signal, and 106 is a digital scan converter (DSC) which converts the blood flow speed data to flow image data and outputs the same. The beam former 3501 also forms an ultrasonic beam having a direction slightly different from the direction of the ultrasonic beam formed by the beam former 102. Reference numeral 3502 is a wave detection circuit which detects the ultrasonic signal output from the beam former 3501, 3504 is a digital scan converter (DSC) which receives as input the detection signal and outputs a B mode image data, 3503 is a color Doppler analysis unit which calculates the blood flow speed data from the ultrasonic signal, and 3505 is a digital scan converter (DSC) which converts the blood flow speed data to flow image data and outputs the same. Reference numeral 3506 is a displaying unit which displays the B mode images and the flow images. Even when both of the beam formers 102 and 3501 generate ultrasonic beams for rough scannings, the combined images on the displaying unit 3506 may result, as a whole, in a high density image. In this second conventional method, however, at least a plurality of beam formers is necessary, so inevitably the cost becomes higher and the apparatus becomes larger in size, which is not necessarily satisfactory to the user. The cost reductions made possible by advances in semiconductor technology further cannot be expected to contribute much to beam formers. Figure 36 illustrates the third conventional method. In the figure, components the same as in Fig. 32 are shown by the same reference numerals. Reference numeral 3601 is a control unit which outputs the timing th for performing the interpolation, and 3602 is a weighted averaging unit which performs weighted averaging on the original image data. Reference numeral 3603 is a display unit which displays the B mode images and the flow images. In this method, successive original images are recorded in a original image frame memory 108 and, from the two original images I1 and I2 obtained at the timings t1 and t2 recorded and shown in Fig. 37A and 37E, interpolated images I (x, y) shown in Figs. 37B, 37C, 37D at the designated timing th are calculated by the weighted averaging unit 3602 in accordance with the following equation: I(x, y) = (1 - w)I1(x, y) + w·I2(x, y) where, w = (th - t1)/(t2 - t1) In this method, it is possible to improve the apparent ultrasonic frame rate simply and inexpensively. When as shown in Figs. 37A and 37E, the position and angle of the blood flow differ greatly among original images, however, as shown in Figs. 37B, 37C, and 37D, a false blood flow completely different from the true images shown in Figs. 33B, 33C, and 33D ends up being displayed, presenting the danger of mistaken diagnosis. It is therefore desirable to improve the above three methods and to provide an apparatus which increases the apparent ultrasonic frame rate without the above defect, that is finds from the images of Figs. 33A and 33E the natural interpolated images as shown in Figs. 33B, 33C, and 33D and displays the same. Figure 1 is an explanatory view of the present invention. In the figure, 101 is an ultrasonic probe which sends and receives an ultrasonic wave, 102 is a beam former which forms an ultrasonic beam, 103 is a wave detection circuit which detects the ultrasonic signal output from the beam former 102, 104 is a digital scan converter which receives as input the detection signal and outputs a B mode image data, 105 is a color Doppler analysis unit which calculates the blood flow speed data from the ultrasonic signal, and 106 is a digital scan converter which converts the blood flow speed data to flow image data and outputs the same. Note that the transmitter 100 shown in Fig. 32 is omitted here only to simplify the drawing. Actually, the transmitter 100 is, of course, connected to the ultrasonic probe 101. Reference numeral 107 is a switch which switches the path of the flow image data, 108 and 109 are frame memories which record the original image data, 110 and 111 are shape parameter calculating units which calculate the shape parameters, i.e. parameters characterizing the shape of the region where blood flows in the original image (hereinafter referred to as blood flow regions), relating to the shape of the blood flow regions, 112 is a shape parameter interpolating unit which interpolates the shape parameters to calculate the interpolated shape parameters, 113 is an image converting unit which uses the shape parameters and the interpolated shape parameters to perform image conversion on original images and obtain interpolated images, 114 is an interpolated image frame memory which records the interpolated images, 115 is a control unit which gives a designated timing for calculation of the interpolated images to the shape parameter interpolating unit, and 116 is a displaying unit which displays the original images, interpolated images, and B mode images. The ultrasonic color Doppler diagnostic apparatus embodying the present invention, as shown in Fig. 1, is provided with shape parameter calculating units 110 and 111 which calculate the shape parameters of the original images, a shape parameter interpolating unit 112 which finds the shape parameters at any timing from the shape parameters of the original images, an image converting unit 113 which obtains interpolated images from the original images, and a displaying unit 116 which displays the interpolated images in between the original images. The blood flow in the heart changes direction and position with each instant. If simply interpolated by the third conventional method, a false blood flow will appear, for example a single blood flow will appear as two flows in the interpolated images, or other extremely unnatural images will be produced. The central concept in the present invention is to calculate shape parameters so as to investigate how the blood flow moves, turns, expands and contracts in the successive original images and to perform image conversion from the original images based on the results to find interpolated images and thereby obtain natural interpolated images. According to the above construction, it is examined how the blood flow regions move, turn, expand, and contract with each original image and then interpolated images are created from the original images, so the natural interpolated images as shown in Figs. 33B, 33C, and 33D are obtained while holding the same precision as with the original images and without any appearance of false blood flows and thus facilitate an increase in apparent ultrasonic frame rate. Figure 2 shows a first embodiment of the present invention. In the figure, components the same as in Fig. 1 are shown by the same reference numerals. Reference numeral 201 is a shape parameter linear interpolating unit which performs linear interpolation on the shape parameters to calculate the interpolated shape parameters. In this embodiment, ellipses are fit as shown in Figs. 3C and 3D on the blood flow regions on the original images of Figs. 3A and 3B as physical images and it is determined how the latter change from the ellipses of Fig. 3C and Fig. 3D to the ellipse as in Fig. 3E. Based on this rule, an interpolated image shown in Fig. 3F is obtained from the original image shown in Fig. 3A to obtain an interpolated image which can express a natural blood flow region. The parameters necessary for expressing an ellipse are the coordinates of the center of the ellipse, the direction of the minor axis, the length of the major axis, and the length of the minor axis and correspond to the five shape parameters discussed below, that is, the x coordinate X of the center of gravity, the y coordinate Y of the center of gravity, the angle  which the minor axis forms with the x axis, the inertia moment K about the minor axis, and the inertia moment L about the major axis. The work for fitting the ellipse means to find these shape parameters. In the shape parameter calculating unit 110, the original image I1 (x, y) is read out from the original image frame memory 108 and the values of the pixels are replaced by absolute values of the same, then if the values of the pixels exceed a threshold level of a low level set in advance, the values as they are are used, while if they do not exceed it, the pixel values are replaced by 0, so as to obtain a value J1 (x, y) of a pixel of an image for calculation of the shape parameters. Hereinafter, the value of a pixel of an image is simply referred as an image. It is assumed that J = J1 , then the following arithmetic operations are performed so as to calculate the five shape parameters of the x coordinate X of the center of gravity, the y coordinate Y of the center of gravity, the angle  which the minor axis forms with the x axis, the inertia moment K about the minor axis, and the inertia moment L about the major axis by the following equations: X = Mx/M0 Y = My/M0  = (1/2)·arctan(2·µxx/(µxx - µyy)) K = (1/2)·((µxx + µyy) + ((µxx - µyy) 2 + 4µxy2))) L = (1/2)·((µxx + µyy) - ((µxx - µyy) 2 + 4µxy2))) where, M0 = ∬ J(x, y)dxdy (area of J) Mx = ∬ xJ(x, y)dxdy (primary moment of J with respect to the x axis) My = ∬ yJ(x, y)dxdy (primary moment of J with respect to the y axis) µxx = ∬ (x - X)·J(x, y)dxdy/M0 µyy = ∬ (y - Y)·J(x, y)dxdy/M0 µxy = ∬ (x - X)(y - Y)·J(x, y)dxdy/M0 By this, from the output of the shape parameter calculating unit 110, the five shape parameters of the shape parameters X1, Y1, 1, K1, and L1 of the original image (x, y) are obtained. On the other hand, the second original image I2 (x, y) is output from the original image frame memory 109. In the shape parameter unit 111, the above-mentioned processing is performed to obtain the x coordinate X2 of the center of gravity, the y coordinate Y2 of the center of gravity, the angle 2 which the minor axis forms with the x axis, the inertia moment K2 about the minor axis, and the inertia moment L2 about the major axis. These two sets of shape parameters are input to the shape parameter linear interpolating unit 201 to obtain the following interpolated shape parameters: Xh = (1 - w)X1 + w·X2 Yh = (1 - w)Y1 + w·Y2 h = (1 - w)1 + w·2 Kh = (1 - w)K1 + w·K2 Lh = (1 - w)L1 + w·L2 where, w is the weight for obtaining the interpolated images. If the timing at which the original image I1 (x,y) is obtained is t1, the timing at which the original image I2 (x, y) is obtained is t2, and the timing at which the interpolated image is desired to be obtained is th, then the following arithmetic operation is performed: w = (th - t1)/(t2 - t1) and the range of 0 < w < 1 is obtained. Here, illustrating the method of finding Xh, it is learned that linear interpolation as in Fig. 3G is performed. Next, the shape parameters X1, Y1, 1, K1, and L1 and the shape parameters of the interpolated image at the designated timing, that is, the interpolated shape parameters Xh, Yh, h, Kh, and Lh are input to the image converting unit 113 and the interpolated image Ih1 (x, y) is calculated from the original image I1 (x, y). In the image converting unit 113, affine conversion, explained later, is performed. Affine conversion itself is a well known image conversion technique and involves linear computation of three conversions, i.e. a parallel movement, a rotation, and an elongation or contraction. Here, if the conversion for parallel movement is T (X, Y), the conversion for rotation about the origin by exactly an angle  is R (), and the conversion for expansion or contraction K times in the x axial direction and L times in the y axial direction is S (K, L), then what coordinates of pixels of the original image I1 (x, y) the pixel Ih (xh, yh) of the interpolated image corresponds to can be computed by the following equation: x y 1 = G(X1,Y1,1,K1,L1, Xh,Yh,h,Kh,L) xh yh 1 where, G(X1, Y1, 1, K1, L1, Xh, Yh, h, Kh, Lh) = T(X1, Y1) R (1) · S(K1, L1) R (-1) · R(h) S (-Kh, -Lh) · R(-h) T (-Xh, -Yh) Here, T, R and S are as follows: T(X, Y) = 1, 0, 0, 0, 1, 0, X Y 1 R(X, Y) = cost(), -sin(), 0, sin(), cos(), 0, 0 0 1 S(K, L) = K, 0, 0, 0, L, 0, 0 0 1 From this, it is possible to create an interpolated image by making the value Ih (xh, yh) of the pixel on the coordinates (xh, yh) of the interpolated image shown in Fig. 4B the value I1 (x, y) of the pixel on the coordinates (x, y) of the original image shown in Fig. 4A. The x, y found in this way is not necessarily precisely at the center of the pixels of the original image, but as shown in Fig. 4A it is possible to deal with this by using the value I (i, j) of the pixel closest to the coordinate (x, y) or by interpolating from the surrounding four pixels (i - 1, j), (i - 1, j + 1), (i, j), (i, j + 1). Further, when writing in the interpolated image to the interpolated image frame memory 114 and, for example, obtaining three frames of interpolated images with respect to a pair of original images shown in Fig. 5A, a display may be made by the displaying unit 116 at the timing shown in Fig. 5B. The B (brightness) mode image is the image of a muscle. Note that the interpolation is not effected on the B mode images as shown in Fig. 5C because the change rate of the B mode image is very low in comparison with the flow rate of blood. The original image, the interpolated image, or the B mode image is displayed on the displaying unit 116. Figure 6 shows an embodiment of the displaying unit. In the figure, 601 is a selector which selects and outputs one of the flow image data and the B mode image data, 602 is a color lookup table (LUT) which converts the signal input to the color lookup table 602 into an RGB signal and outputs the same, and 603 is a comparator which compares the B mode image data and the threshold level and outputs a logical level signal in accordance with the results. As shown in Fig. 6, if the data of the B mode image is higher than a threshold level determined in advance, then the B mode image data appears at the output of the selector 601. When this is not the case, the flow image data appears. Together with the image data, an RGB signal is output while switching the COLOR LUT. Therefore, the B mode image is displayed at portions where the luminance of the B mode image is high, and otherwise the flow image is displayed. In the above explanation, the original images and interpolated images were displayed, but it is also possible to find the interpolated images at timings of equal intervals, leave out the original images, and display only the interpolated images. Figure 7 shows a second embodiment. In the figure, components the same as in Fig. 1 are shown by the same reference numerals. In the figure, 702 and 703 are image converting means, which use the shape parameters and the interpolated shape parameters to perform image conversion on the original images and obtain the converted images. Reference numeral 704 is a weighted averaging unit, which obtains the weighted average of two converted images in accordance with a designated timing th to obtain an interpolated image. Reference numeral 705 is an interpolated image frame memory which records the interpolated images. In this embodiment, the object is to obtain a higher precision interpolated image than in the first embodiment by performing image conversion not only from the original image I1 (x, y), but also from the original image I2 (x, y) and obtaining the weighted average of the two resulted converted images to obtain a single interpolated image. As in the first embodiment, the shape parameters X2, Y2, 2, K2, and L2 and the interpolated shape parameters Xh, Yh, h, Kh, and Lh are input to the image conversion circuit 703 and the interpolated image Ih2 (xh, yh) is calculated from the original image I2 (x, y). The interpolated images Ih1 (xh, yh) and Ih2 (xh, yh) obtained in this way are input to the weighted averaging means 704, where the weighted average of the pixels of the two interpolated images is output as Ih (xy, yh) = (1 - w) Ih1 (xh, yh) + w·Ih2 (xh, yh) to obtain the desired interpolated image. The shape parameter extracting units 110 and 111, the shape parameter linear interpolating unit 201, the image converting units 702 and 703, and the weighted averaging unit 704 may be easily constructed using a multiplier, adder, divider, etc. so as to operate as in the equation disclosed above. Further, when use is made of an MPU which can operate at a sufficiently fast speed, it is possible to realize the functions of the circuits by software. Also, it is possible to successively process a plurality of images by a single circuit having the same functions such as the image converting units 702 and 703. Figure 8 is a view showing a third embodiment. In Fig. 8, components the same as those in Fig. 7 are shown by the same reference numerals. In the figure, 801 and 802 are original image frame memories which record the original images, 803 and 804 are shape parameter calculating units which calculate the shape parameters showing the shapes of the blood flow regions, and 805 is a shape parameter high order interpolating unit which performs high order interpolation on the shape parameters to obtain interpolated shape parameters. In this embodiment, the object is to obtain a more natural interpolated image by performing high order interpolation on portions of the interpolated image where the shape parameters were calculated by linear interpolation in the second embodiment. The operation of this embodiment is very close to the operation of Fig. 7, so the explanation will focus on the main points of this. In this embodiment, the feature is the use of three or more sets of shape parameters. Here, the explanation will be made of the case of use of four sets of shape parameters. Making the explanation with reference to the X coordinate of the center of gravity position in the shape parameters, four x coordinates X1, X2, X3, and X4 of the center of gravity position are obtained, corresponding to the timings t1, t2, t3, and t4 where the original images were obtained, as shown in Fig. 9, then a third-ordered function passing through all these points is sought. The shape parameter high order interpolating means 805 determines the coefficients a, b, c, and d of the third-ordered function in accordance with the next equation and uses the interpolation timing parameter w designated to output the interpolated value Xh: The other image display parameters Yh, h, Kh, and Lh are calculated based on the same calculations from Y1, 1, K1, L1, Y2, 2, K2, and L2. Even when using N sets of shape parameters, it is easy to find the coefficients of the N-1 order function and find the interpolated shape parameters. Figure 10 is a view explaining a fourth embodiment. In the figure, components the same as in Fig. 2 and Fig. 8 are shown by the same reference numerals. Reference numerals 1001 and 1002 are shape parameter averaging units, which obtain the average of the plurality of shape parameters. In this embodiment, the object is to obtain a more stable interpolated image by creating an interpolated image using average shape parameters obtained by averaging the shape parameters of a plurality of frames when image conversion is performed. For example, for the X coordinate of the center of gravity, as shown in Fig. 11, X1, X2, and X3 among the X1, X2, X3, and X4 obtained corresponding to the timings t1, t2, t3, and t4 are used to obtain an average X2' by the shape parameter averaging unit 1001, X2, X3, and X4 are used to obtain another average X3' by the shape parameter averaging unit 1002, and these average shape parameters are used to obtain the interpolated shape parameters by, for example, the image shape parameter linear interpolating unit 201. Figure 12 shows a fifth embodiment. In the figure, components the same as in Fig. 1 are shown by the same reference numerals. In the figure, 1201 and 1204 are gate circuits which control the flow image data from the digital scan converter of the previous stage to obtain a divided image, 1203 is a sign judging unit which judges the sign of the flow image data from the digital scan converter 106 of the previous stage and outputs the judged sign as a logical level signal. Reference numerals 1202 and 1209 and 1210 represent switches which switch the flow image data output from the gate circuit 1201 or the gate circuit 1204 with each frame, and 1205 to 1208 are divided image frame memories which record the divided images. Reference numerals 1211 and 1212 are interpolated image producing units which are comprised of the shape parameter calculating units 110 and 110, the shape parameter interpolating unit 112, and the image converting unit 113 shown in Fig. 1 and which produce interpolated images from the divided images. In this embodiment, a flow image comprised of a mixture of a blood flow region with a positive average flow rate, which means a blood flow approaching to the ultrasonic probe 101, and a blood flow region with a negative average flow rate, which means a blood flow going away from the ultrasonic probe 101, as shown in Fig. 13A, are handled as separate images as shown in Figs. 13C, 13D, 13E, and 13F according to whether the pixel values of the flow image are positive or negative, thus enabling a separate interpolation of the inherently independently flowing blood flows and further, it is expected, obtaining a more natural interpolated image. The value of the pixels of the flow image is first judged to be positive or negative by the sign judging unit 1203. If positive, the logical level "1", for example, is output and if negative, the logical level "0", for example, is output. By controlling the gate 1201 and the gate 1204 by the output of the sign judging unit 1203, the blood flow region with the negative average flow rate is recorded in the divided image frame memory 1205 as shown in Fig. 13C, while the blood flow region with the positive average flow rate is recorded in the divided image memory 1207 as shown in Fig. 13E. In the next frame, the switches 1210 and 1209 are operated, whereby the blood flow region with the negative average flow rate is recorded in the divided image frame memory 1206 as shown in Fig. 13D, while the blood flow region with the positive average flow rate is recorded in the divided frame memory 1208 as shown in Fig. 13F of the figure. The outputs of the divided image frame memories 1205, 1206, 1207, and 1208 recorded in this way are input to the interpolated image producing units 1211 and 1212, whereby it is'possible to separately obtain an interpolated image of the blood flow region with the positive average flow rate and the interpolated image of the blood flow region with the negative average flow rate and therefore to obtain a more natural image. Further, as shown in Fig. 14, the blood flow speed data of the output of the color Doppler analysis unit 105 may be separated and after separation passed through the DSC's 1401 and 1402 to be recorded in the divided image frame memories 1205 and 1207 or 1206 and 1208. Figure 15 shows a sixth embodiment. In the figure, components the same as those in Fig. 12 are shown by the same reference numerals. Reference numeral 1503 is a mosaic pattern judging unit, which judges if the area surrounding a particular pixel in the flow image forms a mosaic pattern, and 1501 and 1502 are shift registers which give a delay of the processing time of the mosaic pattern judging unit 1503. In this embodiment, a mosaic pattern observed in a so-called jet stream or the like is a special blood flow pattern wherein red portions showing the positive average flow rate and blue portions showing the negative average flow rate appear at random for each pixel. The mosaic pattern is formed when the blood flow is disordered. The mosaic pattern is also formed when the sampling rate is not equal to or greater than twice the highest significant component of the flow rate of the blood, according to the sampling theory. The object is to raise the reliability of diagnosis by extracting the blood flow regions showing a mosaic pattern and finding the interpolated images for them by themselves. The values of the pixels of the flow image are first judged to be mosaic or not by the mosaic pattern judging unit 1503. If the pixels are judged as a mosaic, the logical level "1", for example, is output, and if negative the logical level "0", for example, is output. Figure 16 shows details of the mosaic pattern judging unit 1503. In the figure, 1601 and 1602 are comparators which compare the input signals of flow image data and +Vth or -Vth and output theresults as logical level signals, 1603 to 1608 and 1613 to 1618 are D-flipflops (DFF) each of which gives a delay to one pixel worth of data, 1609, 1610, 1621, and 1622 are shift registers each of which gives a delay corresponding to one scanning line, 1611 and 1619 are number judging circuits each of which judges if the number of signal lines with logical levels of "1" input from the previous stage is larger than a defined value N, 1612 is an invertor, and 1620 is an AND gate. The mosaic pattern judging unit 1503, as shown in Fig. 16, outputs a logical level "1" (hereinafter referred to as true) if the value of the pixel is more than +Vth according to the comparator 1601 and outputs a logical level "0" (hereinafter referred to as false) if not. It extracts the results of comparison of the pixel (i, j) of Fig. 17 and the surrounding eight pixels by the shift registers 1609 and 1610 and the DFF's 1603 to 1608. If, by the number judging circuit 1611, the number of pixels with logical levels true is larger than a number N set in advance, then it outputs a logical level true while if not it outputs a logical level false. The output logical level shows if the pixels of a positive average flow rate are more numerous than a defined number. The number judging circuit 1611 can be easily constructed by a random logic and can be replaced by a ROM. Similarly, if, by the comparator 1602 and the invertor 1612, the pixel is lower than -Vth, it outputs a logical level true and if not outputs a logical level false. It extracts the results of comparison of the pixel (i, j) itself and the surrounding eight pixels by the shift registers 1621 and 1622 and the DFF's 1613 to 1618. If, by the number judging circuit 1619, the number of pixels of a logical level true is larger than a number N previously set, it outputs a logical level true and if not, outputs a logical level false. The output logical level shows if the pixels with a negative flow rate are more numerous than a defined number. The logical product of the output of the number judging circuit 1619 is obtained by the AND gate 1620 and if a mosaic pattern, a logical level true is output. If not, a logical level false is output. The gate 1201 and gate 1204 of Fig. 15 are controlled by the output of the mosaic pattern judging unit 1503, whereby the normal blood flow region is recorded in the divided image frame memory 1207 as shown in Fig. 18E of the figure and the blood flow region with the mosaic pattern is recorded in the divided image frame memory 1205 as shown in Fig. 18C. In the next frame, the switches 1210 and 1209 are switched, whereby the normal blood flow region is recorded in the divided image frame memory 1208 as shown in Fig. 18F and the mosaic pattern blood flow region is recorded in the divided image frame memory 1206 as shown in Fig. 18D. The outputs of the divided image frame memories 1205, 1206, 1207, and 1208 thus recorded are input to the interpolated image producing units 1211 and 1212 to obtain an interpolated image, whereby it is possible to separately obtain an interpolated image of the mosaic pattern blood flow region and an interpolated image of the normal blood flow region, and a more natural image can be obtained. In this embodiment, the judgment was made on a particularly noted pixel and the surrounding eight pixels, but in working this embodiment, it is possible also to suitably select the number of the D-flipflops (DFF's) so as to select the appropriate range of pixels. Figure 19 shows a seventh embodiment. In the figure, components the same as in Fig. 12 are shown by the same reference numerals. Reference numeral 1901 is a binarization circuit which obtains a binary image from an original image, 1904 is a binary image frame memory which records binary images, 1902 is a labeling circuit which gives unique label values to blood flow regions existing independently two dimensionally, 1903 is a label frame memory which records the labels, and 1905 is a decoder which makes just one of the lines a logical level true in accordance with the labeling values of the pixels. Even with blood flow regions with the same blood flow speed data characteristics, it is irrational to create an interpolated image by deeming as one, for example, two blood flows flowing in the same direction simultaneously to the left ventricle and the right ventricle. In this embodiment, the object is to treat as separate the blood flow regions which are clearly separate two dimensionally so as to obtain a natural interpolated image. Using the binarization circuit 1901, pixels of an image are labeled by using two values: 1 for pixels with over an absolute value of the average flow rate and 0 for other pixels and are stored in a binary image frame memory 1904 as shown in Fig. 21A. Next, the labeling circuit 1902 is used so as to scan the pixels on the binary image frame memory 1904 and perform a labeling processing as shown in Figs. 21B to 21D by the next algorithm, which is explained by the flow charts of Figs. 21E and 21F. The label frame memory 1903 shown in Fig. 21B or Fig. 21D stores labels of pixels corresponding to the pixel values stored in the binary image frame memory shown in Fig. 21A. The way to store the labels in the label frame memory 1903 is as follows. In the flowchart, at step S21, the pointer of the raster scan is set on the uppermost left pixel of the binary image frame memory 1904 shown in Fig. 21A. At step S22. raster scan is effected on the binary image frame memory 1904 pixel by pixel. At step S23, a judgement is made of whether the pixel value is "1". If it is not "1", the process goes to step S30 so that a judgement is made of whether the pointer is on the lowermost right of the binary image frame memory 1904. If it is not, the process returns back to step S22 to continue the raster scan. If the pixel value is "1" at step S23, then at step S24, a judgement is made of whether the elements adjacent to the element corresponding to the scanning pixel are already labelled. The labels are positive numbers in this embodiment. Namely, the value "0" is not referred to as a label. If the adjacent elements have not yet been labelled, then at step S25, a new label greater than the already provided number is provided to the element on the label frame memory 1903, and the process goes to step S30. Note that the element provided with the new label corresponds to the pixel under scanning. If the adjacent elements have already been labelled, then at step S26, a judgement is made of whether the adjacent labels are the same to each other. If they are not the same, then at step S27, a new label which is the smallest number in the adjacent labels is provided to the element corresponding to the pixel under scanning. Then, at step S28, an instruction to rewrite a label which is the same as the adjacent label but different to the new label provided to the element under scanning is stored in a memory (not shown in Fig. 19). Then, the process goes to step S30. If the adjacent labels are the same at step S26, then at step S29, the same label as the adjacent labels is provided to the element under scanning. Then the process goes to step S30. At step S30, a judgement is made of whether the pointer is on the lowermost right on the label frame memory 1903. If it is not, the process goes back to step S22. If the pointer is on the lowermost right of the frame memory 1903 at step S30, the process goes to rewriting process shown in Fig. 21F. In Fig. 21F, at step S31, the scanning pointer is set on the uppermost left of the label frame memory 1903. At step S32, a raster scan is effected again. At step S33, a judgement is made of whether the label is the same as the label in the stored instruction. If it is not the same, the process goes back to step S35. If the label is the same as the label in the stored instruction, then at step S34, the label is rewritten in accordance with the instruction stored in the memory at step S28. Then, at step S35, a judgement is made as to whether the pointer is on the lowermost right on the label frame memory 1903. If it is not, the process goes back to step S32. If the answer is yes at step S35, the label rewriting process is completed. The practical labelling process is further explained with reference to Figs. 21A to 21D. After all pixels in the binary image frame memory 1904 are provided with the binary values "0" or "1" as shown in Fig. 21A, raster scan is effected on the binary image frame memory 1904. The first "1" is found on the pixel (3,3) of the memory 1904. Then, it is checked whether the adjacent labels are already provided. In Fig. 21B, the elements (2,2), (3,2), (4,2), and (2,3), which are adjacent to the element (3,3) corresponding to the scanning pixel (3,3) of the memory 1904, are not labelled, i.e., they are "0". Therefore, the element (3,3) of the memory 1903 is labelled "1", because the number "1" is the smallest number in the already provided label. Note that only the upper left (2,2), the direct upper (3,2), the upper right (4,2), and the left (2,3) elements in the adjacent elements are actually checked, and the other adjacent elements (4,3), (2,4), (3,4), and (4,4) are not checked because these elements have not yet been scanned. The second "1" is found on the pixel (5,3) of the memory 1904. Since the elements (4,2), (5,2), (6,2), and (4,3), which are adjacent to the element (5,3) corresponding to the scanning pixel (5,3) of the memory 1904, are not labelled, the element (5,3) is labelled by a new label "2" which is different from the already provided label. The third "1" is found on the pixel (6,3) of the memory 1904. Since the only one adjacent element (5,3) is labelled "2", the element (6,3) corresponding to the pixel (6,3) is labelled "2" (see step S29). The fourth "1" is found on the pixel (3,4) of the memory 1904. Since the only one adjacent element (3,3) is labelled "1", the element (3,4) corresponding to the pixel (3,4) is labelled "1" (see step S29). The fifth "1" is found on the pixel (5,4) of the memory 1904. Since the adjacent elements (5,3) and (6,3) are labelled with the same number "2", the element (5,4) corresponding to the pixel (5,4) is labelled "2" (see step S29). Similarly, the pixels (6,4) and (3,5) are labelled "2" and "1", respectively. Note that, in labelling the pixel (4,5) it is found that the adjacent pixels (3,4) and (3,5) are labelled "1" but the adjacent pixel (5,4) is already labelled "2". In this case, according to step S27, the smallest adjacent label, which is "1" in this case, in provided. Since the pixel (4,5) and the pixel (5,4) are adjacent to each other but the labels of them are different from each other, an instruction to rewrite the label "2" to "1" is stored in the memory at step S28. Similarly, the pixel (5,5) is labelled "1" because the smallest number in the adjacent labels is "1". The pixel (9,5) is labelled "3" because there is no adjacent label and the label "1" and "2" are already provided so that the smallest new label is "3". In the similar way, the pixels (11,5), (4,6) , (9,6) (10,6), (11,6), (8,7), (9,7), and (10,7) are labelled "4", "1", "3", "3"; "3", "3", "3", "3", and "3", respectively. Then, the label rewriting is effected in accordance with the stored instructions. Namely, in scanning the label frame memory, when the label "2" is found, it is rewritten to "1". Similarly, when the label "4" is found. it is rewritten to "3". Thus, the rewritten label frame memory is obtained as shown in Fig. 21D. By the above algorithm, the label is written in the label frame memory 1903. The original image and label are read out by raster scanning simultaneously from the original image frame memory 108 and the label frame memory 1903. Using the decoder 1905, when the label value is 1, the gate 1201 becomes active, while when the label value is 2, the gate 1202 becomes active and the results are stored in the divided image frame memories 1205 and 1207 as shown in Fig. 20C and Fig. 20E. Further, in the next frame, the switches 1210 and 1209 are switched. When after the above-mentioned label processing etc., the label value becomes 1, the gate 1201 becomes active, while when the label value is 3, the gate 1202 becomes active. This stored in the divided image frame memories 1206 and 1208 as shown in Figs. 20D and 20F. The switches 1210 and 1209 may be controlled by the outputs of the decoder 1905. When the number of different labels is three or more, the number of gates and the number of divided image frame memories is also increased. Figure 22 shows an eighth embodiment. In the figure, components the same as in Fig. 7 are shown by the same reference numerals. Reference numeral 2201 and 2202 are shape parameter calculating units which calculate the parameters showing the shape of the blood flow region and the zero order moment M0 of the blood flow region, 2203 and 2207 are switching devices which change the path of the signals based on the control signal, 2204 and 2206 are comparators which compare with previously determined labels and output the results of the comparison as logical level signals, and 2205 is an AND gate. In this embodiment, the object is to find the interpolated image by only the weighted averaging unit when there is no blood flow region in one or more of the original images. Here, in the shape parameter calculating units 2201 and 2202, the output M0 found by the equation (2) is output, and, depending on whether it is above a level previously set, a logical level true or logical level false is output by the comparators 2204 and 2206. The logical product of this is taken by the AND gate 2205, whereby the switch 2203 and 2207 are switched. When there is no blood flow region in at least one image, the image converting units 702 and 703 can be bypassed and an interpolated image can be found by just the weighted averaging unit 704. Figure 23A shows a ninth embodiment. In the figure, 2303 is a display control frame memory which records the displayed and nondisplayed information in pixel units, 2302 is a CPU which initializes 2303 so that only the pixels of the flow rate data of the blood flow speed data are made 1, and 2301 is a gate which controls the display of the interpolated image data. In this embodiment, since there is a possibility of an extremely unnatural image resulting if there is a display of blood flow regions even at portions deviated from the blood flow measurement region where the inherent blood flow speed data was measured, as shown in Fig. 24A, in the obtained interpolated image, the object is to suppress the display other than in blood flow measurement region as shown in Fig. 24B. For example, it is unnatural for a blood flow region to exist in an area outside of the muscle region displayed by the B mode. Figure 23B shows the blood flow measurement region, and Fig. 23C shows the contents of the display control frame memory. As shown in Fig. 23C, the display control frame memory 2303 has written in it from the CPU 2302 a value of 1, corresponding to the logical level true, for pixels in the blood flow speed data measurement range and a value of 0, corresponding to the logical level false, for other pixels. Further, synchronously with the readout of the interpolated image data, the display control frame memory 2303 is read out and the output is used to control the gate 2301, so that the gate outputs blood flow image data having data in only the blood flow speed data measurement range. Figure 25 shows a 10th embodiment. In the figure, 2501 shows an interpolated image frame memory which records interpolated image data of a positive average flow rate, and 2502 is an interpolated image frame memory which records interpolated image data of a negative average flow rate. Reference numeral 2503 is a selector, which selects and passes as the interpolated image data the interpolated image data recorded in one of the interpolated image frame memories 2501 or 2502 in accordance with the control signal, 2504 and 2505 are absolute value circuits which obtain the absolute values of the image data from the interpolated image frame memories 2501 and 2502 of the previous stage, and 2506 is a comparator which compares the interpolated image data made into absolute values from the absolute value circuits 2504 and 2505 of the previous stage and outputs a logical level signal. In this embodiment, the object is to display whichever of the interpolated image data of a positive average flow rate and the interpolated image data of a negative flow rate has a larger absolute value of average flow rate. First, the interpolated image data of a positive average flow rate is stored in the interpolated image frame memory 2501 and the interpolated image data of a negative average flow rate is stored in the interpolated image frame memory 2602. The two are simultaneously read out to obtain the absolute values of the average flow rate at the absolute value circuits 2504 and 2505. At the comparator 2506, whichever is largest is output by the logical level signal and that logical level signal is used to control the selector 2503, whereby one of the interpolated image data of the positive average flow rate and the interpolated image data of the negative average flow rate can be output. Of course, the blood flow image data includes not only average flow rates, but also flow rate dispersion. Here, only in the case where the interpolated image is of a positive average flow rate, it is possible to obtain the interpolated image of the blood flow region of a mosaic pattern as obtained in the sixth embodiment or the interpolated image as obtained in the seventh embodiment and then select out of all the interpolated images the one which has the largest absolute value of average flow rate. Figure 26 shows an 11th embodiment. In the figure, components the same as in Fig. 1 and Fig. 2 are shown by the same reference numerals. Reference numeral 2607 is a switch which switches the path of the B mode image data, 2608 and 2609 are original image frame memories which record the original image data, and 2611 is an interpolated image producing means which produces an interpolated image for the B mode image. The object is to enable an interpolated image to be obtained and further to obtain a natural image by providing an interpolated image producing unit as shown in Fig. 26 for the B mode image too as in the first embodiment. Figure 27 shows a 12th embodiment. In the figure, 2701 is a decoder which converts the NTSC signal into an RGB signal, 2702 is a frame memory which records the image data, 2703 and 2706 are registers which record values temporarily, 2704 and 2707 are dividers which output remainders of the two inputs, and 2705, 2708, and 2710 are gate circuits which pass input signals in accordance with a control signal. Reference numeral 2709 is an average value calculating circuit which obtains the average value of image data recorded in the three parts RGB of the frame memory 2702 of the previous stage, 2711 to 2713 are differential absolute value calculating circuits which output the absolute value of the difference of two inputs, 2714 is an average value calculating circuit which finds and outputs the average value of the three outputs of the differential absolute value calculating circuits 2711 to 2713 of the previous stage, and 2715 is a comparator which compares the predetermined threshold level and the magnitude of the signal from the average value calculating circuit 2714 of the previous stage and outputs the result as a logical level signal. The embodiment is worked with the object of separating the synthesized image of the B mode image and the flow image obtained from the video output from a VTR or ultrasonic diagnostic apparatus into the B mode image and flow image. First, the NTSC signal obtained from the output of the VTR or the other diagnostic apparatus is converted into RGB by the decoder 2701 and recorded in the frame memory 2702. Next, the address (X1, Y1), (X2, Y2) on the color bar shown in Fig. 28 where the largest value of the flow rate data is recorded is accessed and the data stored in the registers 2703 and 2706. Further, the pixels are successively read out, and the differential absolute value calculating circuits 2711, 2712, and 2613, the average value calculating circuit 2714, and the comparator 2715 are used to see if the value of the RGB fluctuates exceeding the threshold level, whereby it is judged if the pixel carries a black and white B mode data or carries a color blood flow speed data and the gates 2705, 2708, and 2710 are controlled to output or not output three types of data, i.e., the flow image data of a positive average flow rate, the flow image data of a negative average flow rate, and the B mode image data. Here, the average value calculating circuit 2709 obtains the average of the R, G, and B data to create a more accurate B mode image data. Further, the dividers 2704 and 2707 are used to normalize the blood flow speed data at the maximum value, whereby it is possible to fetch accurate flow rate data regardless of the level fluctuations of the NTSC signal. Figure 29 shows a 13th embodiment. In the figure, components the same as in Fig. 1 and Fig. 12 are shown by the same reference numerals. Reference numeral 2902 is a switch which outputs the flow image data to any tap, 2903, 2907, 2908 are frame memories which record original images, 2912 and 2913 are switches which select the frame memories in which the original images are recorded, 2901 is a switch which outputs an interpolated image to any tap, 2905 to 2907 and 2909 to 2911 are frame memories which record interpolated images, 2915 is a switch which selects one of the frame memories 2903 to 2911, 2917 is a cine loop memory which records a plurality of B mode images, and 2916 is a switch which selects the path of the B mode image displayed. This embodiment has as its object performing interpolation in the case of use of the cine loop function. Since it does not matter if some time is taken for the production of the interpolated image, it becomes possible to use a device with a relatively low speed for the image converting means etc. and it is possible to perform a plurality of functional blocks having the same function by a single functional block, so reduction of the price can be anticipated. The flow image is, in the same way as the usual cine loop function, recorded in the frame memories 2903, 2907, and 2908 by operating the switch 2902. After freezing, the switch 2915 is used to successively display the frame memories 2903, 2907, and 2908 and it is confirmed that the series of images desired to be interpolated have been recorded. At this stage, there is no difference from the usual cine loop function. Further, by operating the switches 2912 and 2913, interpolated images are produced by the interpolated image producing unit 1211 disclosed in the first embodiment etc., and the switch 2901 is used to record the same in the frame memories 2904, 2905, 2906, 2909, 2910, and 2911. Interpolated images are produced and recorded for all the original image pairs, then the switch 2915 is used to successively display the frame memories 2903 to 2911, whereby it is possible to display everything including the interpolated images. Further, a separate cine loop memory 2917 is provided and the B mode image data is read out from the cine loop memory 2917 at the time of the cine loop function of the blood flow image, whereby it is possible to display the B mode image combined. Also, when using this cine loop function to display the interpolated image, it is necessary to confirm if the image is an interpolated image or a original image. This may be done, when displaying a cursor or graduation showing the frame position of the cine loop, by making the height of the graduation appear low at the position of an interpolate image as shown in Fig. 30A, indicating by a letter, mark, etc. that "displayed image = interpolated image" as shown in Fig. 30B, or making another such display. Further, when a freeze is performed during the display of an interpolated image, the doctor would feel uneasy making a diagnosis by viewing a frozen interpolated image. By controlling the switch 2916 as shown in Fig. 31 so as to stop only at the position of the frame memory, it is possible to freeze at the position of an original image and therefore assist the doctor to make a confident diagnosis. Figure 31 shows the means for freezing only at the position of an original image. In the figure, 3101 is a counter which produces a displayed frame number, 3102 is a frame number conversion table which converts the frame number, and 3103 is a selector which passes one of the two inputs in accordance with a control signal. A frame number displayed by the counter 3101 is produced and the frame number of the original image closest to the frame displayed as shown in Fig. 31B is recorded in the frame number conversion table 3102. The usual operation is for the counter 3101 to continue counting and for the selector 3103 to pass the output signal of the counter 3101 and control the switch 2915. If a freeze signal enters, the counter 3101 stops the count operation, the selector 3103 passes the output of the frame number conversion table 3102, and the switch 2915 is set to the original image. Further, when working this embodiment, use is made of the average speed or the speed dispersion as the blood flow data, but it is also possible to use the Doppler signal power instead. As explained above, according to the present invention there is provided a color Doppler ultrasonic diagnostic apparatus wherein it is possible to produce, insert, and display natural interpolated images between original image frames and it is possible to view the state of the blood flow as if it were changing extremely smoothly, thus contributing much to the improvement of the performance of the color Doppler ultrasonic diagnostic apparatus.

Claims: An ultrasonic color Doppler diagnostic apparatus, for displaying at least two successive frames of two-dimensional images obtained in an ultrasonic interframe time, operable to transmit an ultrasonic pulse in a plurality of directions with respect to a subject, process the signal received, and display the results as a two-dimensional image of the average speed, speed dispersion, or Doppler signal power of blood flowing in the subject, comprising: a shape parameter calculating means (110,111) for calculating the shape parameters characterising the shape of blood flow regions on the original images, a shape parameter interpolating means (112) for calculating shape parameters interpolated at a timing (th) designated in said interframe time from the said shape parameters calculated on the original images, said interframe time, and said designated timing (th), an image converting means (113) for converting the image of at least one of said frames of original images in accordance with the shape parameters at the designated timing (th) found by said shape parameter interpolating means (112) to obtain interpolated images, and a displaying means (116) for displaying as moving images the interpolated images inserted in between the original images or only the interpolated images. An ultrasonic color Doppler diagnostic apparatus as set forth in claim 1, further comprising a weighted averaging means (704) for weighting said interpolated images obtained by said image converting means (702, 703) and for averaging the weighted interpolated images, said weighted averaging means (704) comprising: a first weighting means for weighting, by a value (t2 - th)/(t2 - tl) , a first interpolated image, where t1 is a first timing corresponding to a first frame original image, t2 is a second timing corresponding to a second frame original image, and th is said designated timing, said first interpolated image being obtained by converting, by said image converting means (702, 703), said first frame original image; a second weighing means for weighting a second interpolated image by said value (t2 - th)/(t2 - t1) , where said second interpolated image is obtained by converting, by said image converting means (702, 703), said second frame original image; and an adding means for adding the weighted first and second interpolated images. An ultrasonic color Doppler diagnostic apparatus as set forth in claim 1 or 2, wherein said shape parameter interpolating means (112) is a shape parameter linear interpolating means (201) for performing linear interpolation on the shape parameters of a second frame original image in accordance with the interframe time and the designated timing (th) and thereby calculating interpolated shape parameters. An ultrasonic color Doppler diagnostic apparatus as set forth in claim 1 or 2, wherein said shape parameter interpolating means (112) is a shape parameter high order interpolating means (805) for calculating any function passing through the shape parameters of at least three frames of original images, then for calculating the interpolated shape parameters at the designated timing (th) as values of the function at the designated timing (th). An ultrasonic color Doppler diagnostic apparatus as set forth in claim 1, 2 or 3, further comprising a shape parameter averaging means (1001, 1002) for averaging a plurality of frames worth of shape parameters for each frame calculated in said shape parameter calculating means (110, 111). An ultrasonic color Doppler diagnostic apparatus as set forth in claim 1, further comprising: a characteristic judging means (1203; 1503; 1902, 1903) for judging the characteristic of the average speed, speed dispersion, or Doppler signal power of the blood flowing in a subject at pixels of the original image; and an image dividing means (1205-1208) which divides into a plurality of images the original image in accordance with the characteristic of the average speed, speed dispersion, or Doppler signal power of the blood flowing in the subject; the divided images obtained by the division being deemed as original image and used to find the interpolated images with respect to the divided images. An ultrasonic color Doppler diagnostic apparatus as set forth in claim 6, wherein said characteristic judging means (1203; 1503; 1902, 1903) is a sign judging means (1203) for performing judgment of the sign of the average speed. An ultrasonic color Doppler diagnostic apparatus as set forth in claim 6, wherein said characteristic judging means (1203; 1503; 1902, 1903) is a mosaic pattern judging means (1503) for judging that the number of the pixels having an average speed of over a predetermined speed +Vth and the number of pixels having an average speed less than a predetermined speed -Vth, in the pixels surrounding and including a particularly noted pixel, together are more than a predetermined number so that the pattern is a mosaic one. An ultrasonic color Doppler diagnostic apparatus as set forth in claim 6, wherein the said characteristic judging means (1203; 1503; 1902, 1903) is a labelling means (1902, 1903) for applying the same label to pixels constituting connecting portions for each connecting portion where pixels adjoin and form a single cluster. An ultrasonic color Doppler diagnostic apparatus as set forth in claim 2, further comprising: a blood flow region presence judging means (2204-2206) for judging if there is a region in which blood is flowing in at least one original image in the said two frames; and an image interpolation bypassing means (2203, 2207) which bypasses the said image converting means (702, 703) in accordance with the results of the above detection and thereby directly inputs the original image in the weighted averaging means (704). An ultrasonic color Doppler diagnostic apparatus as set forth in claim 1, wherein the displaying means (116) has a display suppressing means (2301, 2303) which suppresses the display of pixels outside of the range of measurement of the average speed, speed dispersion, or Doppler signal power of blood flowing in a subject. An ultrasonic color Doppler diagnostic apparatus as set forth in claim 6, wherein said displaying means (116) comprises an interpolated image synthesizing means (2501 to 2506) which displays, among the pixels of the interpolated images obtained from the plurality of divided images, the ones with the maximum absolute values of the average speed of the blood flow. An ultrasonic color Doppler diagnostic apparatus as set forth in claim 1, wherein a two-dimensional image of the average speed, speed dispersion, or Doppler signal power of the blood flowing through a subject is used as the original image and at the same time use is made of a B mode image as an original image to produce and display an interpolated image of the B mode image. An ultrasonic color Doppler diagnostic apparatus as set forth in claim 1, further comprising: an image separating means (2711 to 2715) for separating a B mode image and a two-dimensional image of the average speed, speed dispersion, and Doppler signal power of the blood flowing in the subject from an NTSC, RGB, or other image signal; and a flow rate data normalising means (2704, 2707) for normalising the pixel value of the two-dimensional image of the average speed, speed dispersion, or Doppler signal power of blood flowing in a subject, using a pixel value of a color bar showing the correspondence between the average speed, speed dispersion, or Doppler signal dispersion of blood flowing in a subject and color. An ultrasonic color Doppler diagnostic apparatus as set forth in claim 1, further comprising: an original image frame memory (2903, 2907, 2908) for three or more frames, an original image selecting means (2912, 2913) for selecting two frames of original images from the original image frame memory (2903, 2907, 2908), an interpolated image frame memory (2905 to 2907, 2909 to 2911) for storing interpolated images, and a displayed frame selecting means (2915) for selecting any one frame in the original image frame memory (2903, 2907, 2908) and interpolated image frame memory (2905 to 2907, 2909 to 2911), the interpolated image being displayed at the time of reproduction of a cine loop (2917). An ultrasonic color Doppler diagnostic apparatus as set forth in claim 15, further comprising a display format for notifying at the time of cine loop reproduction or freezing if the displayed image is an original image or an interpolated image. An ultrasonic color Doppler diagnostic apparatus as set forth in claim 15, wherein a frame to be frozen at the time of reproduction of the cine loop is specified as an original image frame.

Inventors: MIYAZAKI TOSHIYA, MURAKAMI KEIICHI, SHIBA AKIRA, SHIMURA TAKAKI, TANAHASHI JUNICHI, TORIU TAKASHI, MIYAZAKI, TOSHIYA, MURAKAMI, KEIICHI, SHIBA, AKIRA, SHIMURA, TAKAKI, TANAHASHI, JUNICHI, TORIU, TAKASHI, Miyazaki, Toshiya, c/o Fujitsu Limited, Murakami, Keiichi, c/o Fujitsu Limited, Shiba, Akira, c/o Fujitsu Limited, SHIMURA, TAKAKI, C/O FUJITSU LIMITED, Tanahashi, Junichi, c/o Fujitsu Limited, TORIU, TAKASHI, C/O FUJITSU LIMITED
Applicants: FUJITSU LTD, FUJITSU LIMITED
Application year: 1991
Main classification: A61B8
IPC codes: G01S15, G01S7, A61B8