JP3394648B2 - Ultrasound diagnostic equipment - Google Patents

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ultrasonic diagnostic apparatus, and more particularly to an ultrasonic diagnostic apparatus that forms a three-dimensional image capable of stereoscopically representing an object.

[0002]

2. Description of the Related Art An ultrasonic diagnostic apparatus is an apparatus for forming an ultrasonic image of an object (for example, an organ in a living body) by transmitting and receiving ultrasonic waves, and is used in the fields of biological diagnosis, flaw detection inspection, sonar, etc. There is.

In recent years, various techniques have been proposed for forming a three-dimensional ultrasonic image (hereinafter, three-dimensional image) by transmitting and receiving ultrasonic waves to and from a three-dimensional region. This three-dimensional image has an advantage that an object can be spatially grasped. However, an apparatus capable of forming the three-dimensional image in real time has not yet been put to practical use. Also, there is no provision of a three-dimensional image that can provide a satisfactory spatial representation suitable for diagnostic purposes. This problem has been pointed out especially in the medical ultrasonic diagnostic apparatus, but it seems that there are similar problems in other fields.

[0004]

Therefore, the applicant of the present invention is
Japanese Patent Application No. 7-180107 (unpublished patent application) proposes a new image processing method. This image processing method is based on the well-known volume rendering (Volume Render).
This is a new image processing method adapted to three-dimensional measurement of objects, which is an improvement and development of the dering) method. According to such image processing, a three-dimensional image of an object (stereoscopic image)
Can be formed in real time.

However, although this stereoscopic perspective image gives a powerful image as if an object was taken out of a three-dimensional area and illuminated by light, the stereoscopic perspective image is expressed in black and white shading ( (Monochrome expression)
It is a problem that the image becomes an inorganic or slaughtered image, and the expression is not suitable depending on the property of the object. For example, when a stereoscopic perspective image is formed while emphasizing the surface of a fetus, the body surface is represented in monochrome, resulting in an image representation that is far from the actual color of the fetus (for example, an expression like a formalin pickled sample). It has been pointed out that not only pregnant women but also doctors have a bad impression. It should be noted that even if an object other than a living body is colored in accordance with the pixel value, the visibility can be improved and the image can be easily grasped, and thus such a coloring process has been demanded.

The present invention has been made in view of the above-mentioned conventional problems, and an object thereof is to provide an ultrasonic diagnostic apparatus capable of providing a warm image by coloring a stereoscopic fluoroscopic image as needed. To provide.

Another object of the present invention is to provide an ultrasonic diagnostic apparatus in which the coloring method can be freely set according to the diagnostic application.

Further, an object of the present invention is to provide ultrasonic waves capable of eliminating discomfort when a black-and-white grayscale expression is performed by coloring the body surface similar to that of a stereoscopic fluoroscopic image of a fetus. To provide a diagnostic device.

[0009]

(1) In order to achieve the above object, the present invention forms an in-vivo three-dimensional region by transmitting and receiving ultrasonic waves to and from an in-vivo three-dimensional region including a fetus. By transmitting and receiving the echo data of each voxel and sequentially performing voxel processing using opacity for each echo data along the ultrasonic beam, the pixel value of the pixel corresponding to that ultrasonic beam is determined. determined, thereby sterically fluoroscopic image forming means for forming a three-dimensional fluoroscopic image, a means for converting the pixel values to color information, the surface of the fetus
And a coloring unit that outputs a stereoscopic perspective image that is colored in a flesh color system that is similar to the body surface as a whole .

With the above arrangement, the three-dimensional perspective image formed by the three-dimensional perspective image forming means can be colored by the coloring means, and the colored three-dimensional perspective image can be displayed. Here, by assigning an appropriate color to each pixel value (calculated value), it is possible to eliminate a sense of discomfort when a stereoscopic perspective image is expressed in black and white, or improve visibility. In particular, if the fetus is colored in a skin color system, a lively fetus can be drawn.

[0011]

(2) In a preferred aspect of the present invention, the three-dimensional perspective image forming means calculates opacity α _i of voxel i based on echo data e _i , and opacity calculating means,
And transparency calculating means for calculating a transparency beta _i voxel i based on the echo data e _i, multiplied by the opacity alpha _i in the echo data e _i, a light emission amount calculating means for calculating a light emission amount of the voxel i, 1 previous Of voxel i-1 to the output light quantity of voxel
The transparency β _i of _i is multiplied, and a transmitted light amount calculating means for calculating the transmitted light amount of the voxel i, and a light amount adding means for adding the light emission amount and the transmitted light amount to obtain the output light amount of the voxel i, An image is formed by making the output light amount of the end voxel correspond to the pixel value.

With the above arrangement, the ultrasonic beam is three-dimensionally scanned within the three-dimensional area, and the echo value (that is, echo data) is captured at each position within the three-dimensional area. Here, the three-dimensional region is assumed as a collection of many "voxels". In this model, each voxel corresponds to a sample point (sample volume) and each voxel has an echo value as a "voxel value". Moreover, "opacity" and "transparency" are defined in each voxel as follows.

The voxel processing of each voxel i is performed along a perspective line (which coincides with the ultrasonic beam direction in the present invention). In the voxel processing, first, the opacity α _{i is} calculated based on the echo data e _i of the voxel _i. And transparency β _i is defined. Then, the echo data e _i is multiplied by the opacity α _i to calculate the light emission amount of the voxel i, and the output light amount of the previous voxel i−1 is multiplied by the transparency β _i of the voxel i to obtain the voxel i. Is calculated.

Here, the opacity is related to the degree of diffusion / scattering of ultrasonic waves to the surroundings with respect to the voxel i, and the luminescence amount is considered to represent the strength of the voxel i as a sound source (light source). Be done. On the other hand, transparency is related to the transmittance of ultrasonic waves, and the amount of transmitted light is considered to correspond to the transmittance when voxel i is viewed as a transmission medium. The amount of emitted light and the amount of transmitted light are added to calculate the amount of output light of the voxel i. Here, the output light quantity represents the degree of contribution of the voxel i to the pixel value. This output light amount is passed to the voxel processing (calculation of the transmitted light amount) of the next voxel. When the above voxel processing reaches the final voxel, the output light amount of the final voxel is converted into a pixel value (calculated value). When the pixel value of each perspective line is obtained, one ultrasonic image is formed as a set of those pixel values.

The above voxel processing is sequentially performed from the start voxel on the ultrasonic beam (usually the first voxel closest to the transducer) to the end voxel where a predetermined end condition is satisfied. However, in order to avoid the influence of noise, it is possible not to process the voxels near the transmitter / receiver. In this case, the voxel with a predetermined depth is set as the starting voxel, and the voxel processing is performed from there.

In the present invention, since the voxel processing is executed along the ultrasonic beam, echo data that is sequentially captured can be sequentially processed in real time in the order of time series, and the three-dimensional data required in the conventional apparatus can be obtained. The data memory can be omitted. That is, according to the present invention, the fetched echo data is processed in the fetching order, and the data can be processed without storing all the echo data in the three-dimensional data memory.

It has been confirmed by experiments that the ultrasonic image formed by the above image processing has both the character as a perspective image and the character as a stereoscopic image. That is, the tissue in the living body can be expressed with a watermark like an X-ray photograph, and can be expressed with a sense of depth. Of course, by changing the definitions of the opacity and the transparency, a desired ultrasonic image can be configured, and for example, the transparent feeling or the stereoscopic effect can be emphasized.
Alternatively, the tissue surface can be highlighted or the tissue interior can be highlighted. Such a setting can be automatically performed based on the experimental result, or can be realized by the operator operating the knob in real time while confirming the displayed image.

[0019] (3) In a preferred embodiment of the present invention, and opacity calculating means for calculating the opacity alpha _i voxel i based on the echo data e _i, the echo data e _i, the opacity alpha _i and, Output light amount calculation means for calculating the output light amount C _OUTi of the voxel i based on the input light amount C _INi corresponding to the output light amount of the previous voxel i−1, and the output light amount of the end voxel as the pixel value. The three-dimensional perspective image is formed correspondingly. That is, when the transparency is defined by the opacity, the output light amount is calculated without using the transparency for calculation. Desirably, the output light amount calculation means is C _{OU Ti} = C _INi + α _i · (e _i −C _INi ).
Is calculated.

(4) In a preferred aspect of the present invention, the coloring means is a color palette in which pixel values and hues are associated with each other. Further, in a preferred aspect of the present invention, the color palette has a coloring function that determines a combination of R value, G value, and B value corresponding to each pixel value. Further, in a preferred aspect of the present invention, a color adjusting unit that changes a coloring function in the color palette is provided. With this color adjustment unit, desired coloring can be applied to the stereoscopic perspective image according to the display content. Further, the present invention transmits and receives ultrasonic waves to and from the three-dimensional region in the living body including the fetus, and a transceiving unit that takes in echo data of each voxel that constitutes the three-dimensional region in the living body, and along the ultrasonic beam. A stereoscopic fluoroscopic image forming means for forming a stereoscopic fluoroscopic image of a fetus by sequentially executing voxel processing using opacity defined by the echo data on the echo data of each voxel to obtain pixel values. And a means for converting each pixel value forming the stereoscopic perspective image into color information, wherein each pixel value is converted into color information by a coloring function capable of expressing the surface of the fetus in a skin color system color Coloring means for outputting a stereoscopic fluoroscopic image of the fetus colored in the system. Preferably, it includes an opacity adjusting unit that adjusts the opacity defined by the echo data, and a color adjusting unit that changes the coloring function.

[0021]

DETAILED DESCRIPTION OF THE INVENTION

[Description of Principle of Image Formation] The three-dimensional image forming method (stereoscopic image forming method) in the present embodiment is based on a known volume rendering method.
It is an extension of that technique to real-time image processing. In that case, the conditions specific to the present invention are taken into consideration.
Therefore, first, the principle of the image processing will be described with reference to FIGS.

As shown in FIG. 1A, when an ultrasonic beam directed in the Y direction is scanned in the X direction, a scanning surface 10 is formed. When this scanning surface 10 is moved in the Z direction, a three-dimensional echo data acquisition space 12 is formed as is well known. For this three-dimensional echo data acquisition space 12,
The voxel processing according to the present invention is performed along each ultrasonic beam, and the three-dimensional echo data acquisition space 12 is provided on the projection surface 16.
Is the ultrasonic image 100 of FIG. 1 (B). In the ultrasonic image 100, one line 10 in the X direction
0a corresponds to one scanning surface 10. In other words, one ultrasonic beam (perspective line) corresponds to one pixel in the ultrasonic image 100.

2 and 3, the concept of the voxel 20 is shown. One voxel will
It corresponds to one echo data obtained by the / D conversion, in other words, corresponds to a volume (sample point) corresponding to one cycle of the A / D conversion rate. That is,
The ultrasonic beam is configured as an assembly of many voxels. In FIG. 2, each voxel is shown from i-1 to L _LAST . The value obtained by sequentially performing the processing from the first voxel is the pixel value P (x,
y).

Here, opacity α and transparency β [= (1−α)] are defined for each voxel. The opacity α corresponds to spontaneous light emission around voxels as shown in FIG. The transparency (1-α) corresponds to the degree of transmission of light from the voxel immediately before in that voxel. The opacity α is set in the range of 0 ≦ α ≦ 1, and in the present invention, the opacity is defined as a function of echo data (echo value). Specifically, for example,

## EQU1 ## It is defined as α = k1e ^k2 (1) Here, e is the value of the echo data, and k1 is a constant (coefficient). A value larger than 1 is preferably substituted for k2, for example, k2 = 2 or 3
Is. That is, α changes non-linearly with respect to the value e of the echo data. It is desirable that the constant k1 be variable.

[0025] As shown in FIG. 2, the voxel i, the amount of input light C _INi and the output light amount C _{OU Ti} and is defined, the amount of input light C _INi is one before voxel i-1 of the output light amount C Equivalent to _{OU Ti-1} . That is,

## EQU2 ## There is a relationship of C _INi = C _OUTi-1 (2). However, C _{IN 1} = 0 at the start voxel where the voxel processing is started.

For each voxel, the amount of emitted light and the amount of transmitted light are defined based on the opacity α and the transparency (1-α). That is, the light emission amount of voxel i is defined as the product of opacity and echo data, and is α _i · e _i . The transmitted light amount of the voxel i is defined as the product of the transparency and the input light amount, and is (1-α _i ) · C _INi .

In the present invention, as shown in FIG. 4, the emitted light amount and the transmitted light amount are added as follows to determine the output light amount C _{OUTi of the} voxel.

[0028]

[Equation 3] C _OUTi = (1−α _i ) · C _INi + α _i · e _i (3) However, from the above second formula, C _INi = C _OUTi−1 . That is, the calculation result of the previous voxel is used for the calculation of the next voxel.

While the above third equation is sequentially performed from the start voxel to the next voxel and then to the next voxel, the opacity α _i of each voxel is added, and the added value Σα _i is 1. The process is terminated when the value reaches. However, the processing is also terminated when the processing reaches the last or the voxel L _{LAST of the} set depth. That is,
The processing termination condition is

Σα _i = 1 or i = L _LAST (4) The end of the processing with Σα _i = 1 means that the processing is stopped when the sum of the opacity reaches 1.
Of course, the condition of the above-mentioned fourth expression, especially the maximum addition value of α _i (end determination value) may be changed according to the condition.

The output light-amount C _{OU T} of [0030] or more voxels in the termination determination is made when (final voxel) is utilized as the pixel value P of the corresponding pixel (x, y). Then, when the pixel value calculation for each ultrasonic beam is performed for all ultrasonic beams, the pixel values of all the pixels forming the ultrasonic image can be obtained. That is, an ultrasonic image is formed.

As shown in the third equation, the pixel value P of the pixel
The values of all the echo data from the start voxel to the end voxel are reflected in (x, y). But,
It is a reflection of both the scattering and absorption of ultrasonic waves at each voxel, not just simple integration as in the past. Therefore, it is possible to configure an ultrasonic image having a sense of depth (stereoscopic effect) and a transparency like an image formed by light emitted from a light source, scattered and absorbed by each voxel, and then transmitted.

By the way, in the above third equation, the transparency is defined by (1-α _i ), that is, the transparency can be expressed by the opacity α _i , and therefore the concept of transparency is apparently deleted from the arithmetic expression. be able to. Therefore, the output light quantity C _OUTi can be calculated based on the same principle by _modifying the third expression as follows.

[0033]

[ _Equation 5] C _OUTi = (1−α _i ) · C _INi + α _i · e _i (3) = C _INi + α _i · (e _i −C _INi ) ... (5-1) = C _INi + Δ _i (5-2) (where Δ _i = α _i · (e _i −C _INi )) The above equation 5-1 is a rewrite of the third equation, and if the second term is replaced with Δ _i , Equation 5-2 is obtained. That is, the output light amount C _OUTi of the voxel i is _equal to the input light amount C
It is defined as the sum of the corrected amount delta _i in _INi.
Also in this 5-2 formula, as is apparent from the process of the above formula transformation, the concept of transparency (1-α _i ) is included and does not differ in principle.

[Preferred Embodiment] A preferred embodiment of the present invention will be described below with reference to the drawings.

FIG. 5 shows the overall configuration of the ultrasonic diagnostic apparatus according to the present invention, and FIG. 5 is a block diagram thereof.

In FIG. 5, the ultrasonic probe 21 for taking in three-dimensional data is composed of an ultrasonic transducer and a scanning mechanism for scanning it. As the ultrasonic oscillator, a linear array type oscillator is used in the present embodiment, but a convex type oscillator may be used as a matter of course. The ultrasonic transducer is electronically scanned (linear scan, sector scan),
As a result, the scanning surface 10 (see FIG. 1) is formed in the XY plane. The three-dimensional echo data acquisition space 12 as shown in FIG. 1 is formed by mechanically scanning the scanning surface 10 in the Z direction by the scanning mechanism. In this embodiment, the ultrasonic transducer is automatically scanned in the Z direction by the scanning mechanism, but of course, the ultrasonic transducer may be manually scanned.

In FIG. 5, the transmitting / receiving section 30 supplies a transmission signal to the ultrasonic transducer and processes a reception signal output from the ultrasonic transducer. here,
Although not shown, the received signal is amplified by an amplifier and then logarithmically amplified by a LOG amplifier.
Then, after being converted into a digital signal by the A / D converter, it is sent to the stereoscopic perspective image forming unit 38.

The stereoscopic fluoroscopic image forming section 38 is based on the above-mentioned principle, and the stereoscopic fluoroscopic image (Vol-mode (Vol-mo
de) image) and functions as a so-called three-dimensional image forming unit. This three-dimensional perspective image forming unit 38
The image information (pixel value) output from is input to the color palette 46, and the stereoscopic perspective image is colored. The color palette 46 has, for example, a coloring function as shown in FIG. 7, and in FIG.
The coloring function is shown for each color. That is, for each pixel value (calculated value) of each pixel by voxel processing, R
The GB combination (combination of color information) is determined. In the coloring function of R (red), the distribution ratio of R is
It linearly increases up to a predetermined value near the center, and is a constant value in a region beyond that. In the G (green) coloring function, the distribution ratio of G linearly increases to the vicinity of the maximum calculated value, and becomes a constant value in the region beyond that. B
In the (blue) coloring function, the distribution ratio of B is constant up to a predetermined value close to the minimum value, and linearly decreases in a region above that. These functions are suitable for coloring the fetus, for example.

RGB output from the color palette 46
Each value of is input to the display control unit 40. The display control unit 40 has a function of forming a display image and forms a color stereoscopic image. Then, the color stereoscopic transparent image is displayed on the display 42. A D / A converter is provided between the display control unit 40 and the display 42, but is not shown.

The color adjusting unit 48 is composed of three dials corresponding to RGB and the like.
8 can be used to arbitrarily change the coloring function of the color palette 46. Therefore, it is possible to perform appropriate coloring according to the diagnostic application.

FIG. 8 shows a stereoscopic perspective image by the black and white method and a stereoscopic perspective image by the color palette method according to the present invention. In black and white mode, the entire surface of the fetal <br/> children as shown were feeling uncomfortable becomes gray representation, according to the color palette system, as illustrated
In addition, it is possible to effectively apply a skin-colored or pink-colored color to the entire surface of the fetus to form a lively and warm image of the fetus.

FIG. 6 shows a concrete configuration example of the three-dimensional perspective image forming section 38 shown in FIG.

In FIG. 6, the echo data e _i after A / D conversion is once latched by the latch circuit 50, and then the echo data e _i is emitted light amount calculation unit 52, opacity calculation unit 54 and transparency calculation unit. 56 is input. Here, the light emission amount calculation unit 52 is composed of a multiplier 58, and the multiplier 58 calculates e _i × α _i to obtain the light emission amount. The opacity calculator 54 uses α in this embodiment.
It is composed of a ROM, that is, a table showing the relationship between the echo data e _i and the opacity α. Similarly, the transparency calculator 56 is composed of a (1-α) ROM, that is, a table showing the relationship between the echo data e _i and the transparency (1-α).

Therefore, when the echo data e _i is input to the opacity calculator 54, the opacity α _i is output from the output, while the echo data e _i is transmitted to the transparency calculator 5.
6 is input, the transparency (1-α _i ) is output from the output.

A sampling clock is supplied to the opacity calculating section 54, the transparency calculating section 56, the latch circuit 50, the latch circuit 60 and the latch circuit 62 through an AND gate 64. This sampling clock is a sampling clock input to the A / D converter. That is, each circuit shown in FIG. 6 operates in synchronization with the operation of the A / D converter.

The transmitted light amount calculation unit 66 includes a transparency calculation unit 56.
The output light amount C of the voxel immediately before which is latched by the latch circuit 62 with respect to the transparency (1-α _i ) output from
_OUTi-1 is multiplied, and specifically, it is composed of a multiplier 68. That is, the transmitted light amount calculation unit 66 outputs the transmitted light amount obtained by multiplying the input light amount of the voxel by the transparency.

The light amount adding section 70 adds the light emitting amount and the transmitted light amount based on the above-mentioned third equation, and outputs the output light amount C _{OUTi of the} voxel. Specifically, the light quantity addition unit 70 is configured by an adder 72. Light intensity adder 7
The output light amount C _OUTi output from 0 is sent to the latch circuit 74 having a gate function and the above-mentioned latch circuit 62. That is, the output light amount of the voxel is fed back through the latch circuit 62 for the calculation of the next voxel. The end determination unit 77 determines the end of the above-described voxel processing performed along the ultrasonic beam, and specifically, the adder 76, the latch circuit 60, and the comparator 7.
It is composed of 8. The opacity α _{i of the} voxel is sequentially input to the adder 76.
The output of is fed back through the latch circuit 60 and added to the adder 76.
Is input to the other input of the
As the output of 6, the integrated value obtained by sequentially integrating the opacity is output. The comparator 78 compares the integrated value with a predetermined coefficient K, and outputs an end determination pulse when they match. Specifically, 1 is set as K, the end determination unit 77 integrates the opacity, and outputs an end determination pulse when the integrated value reaches 1. The end determination pulse is input to the AND gate 64 to stop the passage of the sampling clock and the latch circuit 74.
Output light amount C output from the light amount adding section 70
_{Allow OUTi} to latch or pass. The output light amount C _OUTi is the brightness value P of the pixel corresponding to the ultrasonic beam.
It becomes (x, y). Here, the output light amount C _OUTi can be made to correspond to the hue.

Although not shown in FIG. 6, when the processing reaches the voxel of the set depth, the end judging section 76 stops the processing of echo data as described above. Alternatively, when the processing has proceeded to the last voxel of the ultrasonic beam, the processing is stopped. The starting voxel on the ultrasound beam, which is not shown in FIG. 6, is set as the first existing voxel of the starting voxel,
Alternatively, it is set as a voxel having a depth set automatically or artificially. In this case, it is desirable to provide a start voxel setter that sets the conditions of the start voxel.

As described above, according to the circuit configuration shown in FIG. 6, voxel processing is started for each ultrasonic beam from the start voxel along the ultrasonic beam, and the voxel processing is performed for each voxel. At that time, the output of the light quantity adding unit 70 is used in the next voxel processing. Then, the output light amount of the final voxel is used as the pixel value P of the pixel corresponding to the ultrasonic beam. After the processing for one ultrasonic beam is completed, the processing for the next ultrasonic beam is performed, and finally the processing of the echo data for one ultrasonic image is completed. Then, the colored ultrasonic image is displayed on the display 42.

In this embodiment, the opacity is determined according to the function shown in the above-mentioned first equation, and k1 in the first equation can be adjusted by an opacity adjusting section (not shown). That is, the opacity adjusting unit can adjust the depth of expression, and the transparency and the stereoscopic effect.

[0051]

As described above, according to the present invention,
If necessary, the stereoscopic perspective image can be colored to provide a warm image. Further, according to the present invention, the coloring method can be freely set according to the purpose of diagnosis.
Further, according to the present invention, in particular, when a stereoscopic fluoroscopic image of a fetus is formed, coloring similar to the body surface thereof can be applied to eliminate a feeling of strangeness when performing black and white shading expression.

[Brief description of drawings]

FIG. 1 is a diagram showing a relationship between a three-dimensional echo data acquisition space and a projected image.

FIG. 2 is a diagram showing a relationship between an input light amount and an output light amount of each voxel.

FIG. 3 is a diagram showing a light emission amount of each voxel.

FIG. 4 is a diagram for explaining an output light amount of a voxel.

FIG. 5 is a block diagram showing an overall configuration of an ultrasonic diagnostic apparatus according to the present invention.

FIG. 6 is a diagram showing a specific configuration example of a stereoscopic perspective image forming unit shown in FIG.

FIG. 7 is a diagram showing a specific example of a coloring function included in a color palette.

FIG. 8 is a diagram showing a display example of a monochrome method and a display example of a color palette method.

[Explanation of symbols]

21 three-dimensional data capturing ultrasonic probe, 38 three-dimensional perspective image forming unit, 46 color palette, 48 color adjusting unit, 52 light emission amount calculating unit, 54 opacity calculating unit, 5
6 transparency calculation part, 66 transmitted light amount calculation part, 70 light amount addition part, 77 end determination part.

─────────────────────────────────────────────────── ─── Continuation of front page (72) Inventor Masanori Hirose 6-22-1, Mure, Mitaka City, Tokyo Aloka Co., Ltd. (56) References JP-A-60-202318 (JP, A) JP-A-3 -231649 (JP, A) JP 5-101195 (JP, A) JP 5-146432 (JP, A) JP 7-265303 (JP, A) JP 8-7124 (JP, A) ) JP-A-10-33538 (JP, A) Tsuyoshi Mochizuki, Mutsuhiro Akahane, Masanori Hirose, Eiji Kasahara, Development of high-speed projection display (Vol-mode) device aiming at real-time three-dimensional ultrasonic display, Japan Super Proceedings of the 67th Research Conference of Sonic Medicine, Japan Society of Ultrasonics, April 26, 1996, Page 298, Fumihiko Wakao, Tomoyuki Fujita, Kozo Hanai, Kenichi Takayasu, Yukio Muramatsu, Takayoshi Furukawa. , Kyosuke Ushio, Noriyuki Moriyama, Third image of abdomen by helical CT, Monthly new medical care, MEE Promotion Association, October 1, 1994, Volume 21, No. 10, 38, 52-54 (58) Fields investigated (Int.Cl. ⁷ , DB name) A61B 8/00

Claims (8)

(57) [Claims] 1. A transmitting / receiving means for transmitting / receiving ultrasonic waves to / from a three-dimensional region in a living body including a fetus and taking in echo data of each voxel forming the three-dimensional region in the living body, and an ultrasonic beam. By sequentially performing voxel processing using opacity for each echo data, the pixel value of the pixel corresponding to the ultrasonic beam is obtained, and
A stereoscopic fluoroscopic image forming means for forming a stereoscopic fluoroscopic image of the fetus, and means for converting the pixel values into color information,
An ultrasonic diagnostic apparatus comprising: a coloring unit that outputs a stereoscopic perspective image in which the entire surface is colored in a skin color system similar to the body surface . 2. The apparatus according to claim 1, wherein the stereoscopic perspective image forming means calculates an opacity α _i of a voxel i based on echo data e _i , and an echo data e _i based on the echo data e _i . and transparency calculating means for calculating a transparency beta _i voxel i, multiplied by the opacity alpha _i in the echo data e _i, voxel i
And a transmitted light amount calculating means for calculating the transmitted light amount of the voxel i by multiplying the output light amount of the previous voxel i-1 by the transparency β _i of the voxel i, Light quantity adding means for adding the quantity and the transmitted light quantity to obtain the output light quantity of the voxel i, wherein the stereoscopic image is formed by making the output light quantity of the end voxel correspond to a pixel value. Ultrasonic diagnostic equipment. 3. A device according to claim 1, and opacity calculating means for calculating the opacity alpha _i voxel i based on the echo data e _i, the echo data e _i, the opacity alpha _i and,, 1 Input light quantity C _INi corresponding to the output light quantity of the previous voxel i-1
Output light amount calculation means for calculating the output light amount C _OUTi of the voxel i, and the three-dimensional perspective image is formed by making the output light amount of the end voxel correspond to a pixel value. Diagnostic device. 4. The ultrasonic diagnostic apparatus according to claim 1, wherein the coloring unit is a color palette in which pixel values and hues are associated with each other. 5. The apparatus according to claim 4, wherein the color palette includes an R value and a G value corresponding to each pixel value.
An ultrasonic diagnostic apparatus having a coloring function for determining a combination of a value and a B value. 6. The ultrasonic diagnostic apparatus according to claim 4, further comprising a color adjusting unit that changes a coloring function in the color palette. 7. A transmission / reception means for transmitting / receiving ultrasonic waves to / from a three-dimensional region in a living body including a fetus and taking in echo data of each voxel forming the three-dimensional region in the living body, and the ultrasonic beam along the ultrasonic beam. With respect to the echo data of each voxel, a voxel process utilizing the opacity defined by the echo data is sequentially executed to obtain a pixel value, and thereby a stereoscopic fluoroscopic image forming means for forming a stereoscopic fluoroscopic image of the fetus A means for converting each pixel value forming the three-dimensional perspective image into color information, wherein each pixel value is color information by a coloring function capable of expressing the entire surface of the fetus in a flesh color similar to the body surface. An ultrasonic diagnostic apparatus comprising: a coloring unit that outputs a stereoscopic fluoroscopic image of the fetus that has been converted into a skin color system and is colored. 8. The apparatus according to claim 7, further comprising: an opacity adjusting unit that adjusts an opacity defined by the echo data; and a color adjusting unit that changes the coloring function. Sound wave diagnostic equipment.