USRE35798E - Three-dimensional image processing apparatus - Google Patents
Three-dimensional image processing apparatus Download PDFInfo
- Publication number
- USRE35798E USRE35798E US08/547,152 US54715295A USRE35798E US RE35798 E USRE35798 E US RE35798E US 54715295 A US54715295 A US 54715295A US RE35798 E USRE35798 E US RE35798E
- Authority
- US
- United States
- Prior art keywords
- voxel data
- projection plane
- extracting
- designating
- distances
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Images
Classifications
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
- G06T11/00—2D [Two Dimensional] image generation
- G06T11/003—Reconstruction from projections, e.g. tomography
- G06T11/008—Specific post-processing after tomographic reconstruction, e.g. voxelisation, metal artifact correction
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
- G06T17/00—Three dimensional [3D] modelling, e.g. data description of 3D objects
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S378/00—X-ray or gamma ray systems or devices
- Y10S378/901—Computer tomography program or processor
Definitions
- the present invention relates to a three-dimensional image processing apparatus and, more particularly, to a three-dimensional image processing apparatus for displaying soft tissues (also called as parenchyma) of a human body such as an epidermis and a blood vessel.
- soft tissues also called as parenchyma
- An example of a display method of soft tissues is a method of reconstructing a given section using a plurality of parallel CT images (sagittal, coronal, and oblique images).
- a display method of soft tissues is a method of reconstructing a given section using a plurality of parallel CT images (sagittal, coronal, and oblique images).
- each image is a section, positional relationship between the images cannot be easily recognized. As a result, it is difficult to allow three-dimensional recognition of the object.
- an object of the present invention to provide a three-dimensional image processing apparatus which can three-dimensionally display an object without damaging its original information and hence can support simulation in planning an operation.
- a plurality of second voxel data which represent three-dimensional objects of tissues is extracted from first voxel data which represents a three-dimensional object, a distance between a predetermined projection plane and each second voxel data in a three-dimensional space is obtained, and a surface image is formed in accordance with a distance of the second voxel data which is closest to the projection plane. Then, the projection plane is moved in the three-dimensional space close to a memory space of the second voxel data, thereby simulating a surface image obtained when the three-dimensional image is cut.
- axial, sagittal, and coronal sectinal data are extracted from voxel data which represents a three-dimensional object.
- These sectional data are affine-transformed and combined on the basis of a view direction to form a volume multi-plane reconstruction (MPR) image.
- MPR volume multi-plane reconstruction
- the above surface and volume MPR images are combined and displayed in a multi-frame manner.
- FIG. 1 is a block diagram of a first embodiment of a three-dimensional image processing apparatus according to the present invention
- FIG. 2 is a perspective view of voxel data which represents a three dimensional object
- FIGS. 3A, 3B, and 3C are perspective views of voxel data of an epidermis, a bone, and a blood vessel extracted from the voxel data shown in FIG. 2;
- FIG. 4 is a plan view of surface image according to the first embodiment which simulates cutting
- FIG. 5 is a schematic view for explaining distance data according to the first embodiment
- FIG. 6 is a flow chart of an operation of the first embodiment
- FIG. 7 is a block diagram of a second embodiment of the three-dimensional image processing apparatus according to the present invention.
- FIGS. 8A, 8B, and 8C are perspective views showing an operation procedure of the second embodiment
- FIG. 9 is a plan view of multi-frame display as an example according to the second embodiment.
- FIG. 10 is a plan view of multi-frame display combined of an image according to the first embodiment and that according to the second embodiment;
- FIG. 11 is a perspective view of a combination display of a surface image and a volume multi-plane reconstruction image.
- FIG. 12 is a perspective view of a combination display of a surface image and an oblique image.
- FIG. 1 is a block diagram of a first embodiment.
- a plurality of tomographic image data (multilevel data having a density gradation) acquired by an X-ray apparatus, an MRI (magnetic resonance imaging) apparatus, or the like is stored in three-dimensional memory 10 as voxel data. If resolution in a direction perpendicular to a slice (tomographic section) is poor in the actual tomographic image data, data between slices is obtained by interporation.
- FIG. 2 shows such voxel data.
- voxel data concerns a head portion of a human body.
- Read address generator 12 is connected to memory 10.
- the output terminal of memory 10 is connected to level detector 14.
- Detector 14 has a plurality of ranges of CT value and binarizes an output from memory 10 in accordance with each range. This is, when the output from memory 10 has a value within a predetermined range, detector 14 supplies a signal of level "1". Otherwise, detector 14 supplies a signal of level "0".
- ranges including CT values of an epidermis, a bone, and a blood vessel are used as predetermined ranges, binary voxel data of the epidermis, the bone, and the blood vessel can be written in three-dimensional memories 16a, 16b, and 16c as shown in FIGS. 3A, 3B, and 3C, respectively.
- Generator 12 is also connected to memories 16a 16b, and 16c.
- Outputs from memories 16a, 16b, and 16c are supplied to distance detector 18.
- Detector 18 detects a distance from a projection plane to a three-dimensional object assuming that the three-dimensional object is projected from a given view point to the projection plane.
- parameters for defining the projection plane and a view direction are input to detector 18.
- parameters defining the projection plane coordinates of two points on the diagonal line of the projection plane a distance between a center of the voxel and the projection plane, and the matrix size of the projection plane are input.
- As parameter defining the view direction coordinates of two points on the line along the view direction are input.
- FIG. 5 shows this distance. Assuming that a distance between projection plane 50 and predetermined plane 52 parallel to projection plane 50 is D, distance d from projection plane 50 to three-dimensional object 54 is detected. If distance D is known, distance d can be obtained by detecting longest distance D-d from plane 52 to object 54.
- Detector 18 sequentially updates addresses of pixels which are two-dimensionally arranged in a matrix manner to constitute the projection plane from the one on the projection plane (pixel) along a direction perpendicular thereto and detects an updating count of the addresses until voxel data of "1" appears as a distance between the projection plane and the three-dimensional object.
- a detection method of the distance is not limited to this, but any other similar methods may be adopted.
- the distance from voxel data of each tissue to the projection plane is obtained to form a surface image of each tissue as will be described later.
- Detector 22 detects a minimum value of the outputs from Z-buffers 20a, 20b, and 20c, i.e. a distance between the projection plane and the three-dimensional object which is closest to the projection plane of the three-dimensional objects of the epidermis, the bone, and the blood vessel. Then, detector 22 writes a detected value (minimum distance) in an address corresponding to a pixel of two-dimensional memory 24 having an address matrix corresponding to a pixel matrix of the projection plane. A write address for memory 24 is generated by write address generator 26.
- the minimum distance is detected. If a distance is obtained as a negative value upon subtraction, this distance is excluded from minimum distance detection assuming that a tissue represented by the distance is already removed by cutting.
- Distance data output from memory 24 is supplied to surface image generator 28.
- Generator 28 performs shading of two-dimensional image data including the distance data to generate a surface image and displays the surface image which is partially cut as shown in FIG. 4 on monitor 30.
- Write address generator 12 level detector 14, and memories 16a, 16b, and 16c constitute an extraction portion of images of the epidermis, the bone, and the blood vessel.
- Write address generator 26, distance detector 18, Z-buffers 20a, 20b, and 20c, and minimum detector 22 constitute a distance data formation portion.
- the view direction parameter is changed and the same processing is repeated.
- the voxel data concerning the epidermis and the blood vessel which are excluded by cutting must be changed from "1" to "0" in memories 16a and 16b, respectively.
- a minimum value of distance d from the projection plane to a position at which data is "1" is obtained.
- a detector for detecting a maximum value of data I (z) may be provided instead of the minimum detector.
- surface images of a variety of tissues can be displayed in a single three-dimensional space so that a positional relationship between the objects obtained when viewed from a predetermined projection plane is recognized well.
- tissues e.g., an epidermis, a bone, and a blood vessel can be sequentially displayed in the order named, thereby enabling simulation of an operation.
- step 62 is a step for obtaining distances from the projection plane to the respective voxel data in the cutting area
- step 64 is a step for obtaining a minimum value of the distances to the respective three-dimensional images in the cutting area
- step 66 is a determination step for interactively performing this simulation. In this case, until a desired simulation image is obtained, steps 62 and 64 are repeated by changing a cutting area and a cutting depth. Steps 62 and 64 relate to a provisional cutting operation.
- step 66 data concerning the cutting area and the cutting depth of data stored in three-dimensional memories 16a, 16b, and 16c are set to be 0 in real cutting step 68. Therefore, voxel data of each tissue can be removed in accordance with cutting. Thereafter, in step 70, the data in memories 16a, 16b, and 16c are subjected to handling processing (rotation and parallel movement) to change the view direction.
- an output from three-dimentional memory 74 is supplied to section extraction circuit 78 through interpolation circuit 76.
- voxel data is written in memory 74.
- Interpolation circuit 76 interpolates data between slices.
- Section extraction circuit 78 extracts sectional data of axial, coronal, and sagittal sections from the voxel data.
- FIG. 8A A relationship between the axial, coronal, and sagittal sections is shown in FIG. 8A.
- Parameters for specifying positions of the respective sections are input by an ROI (region of interest) input such as a tracker ball.
- the sectional data of the axial, coronal, and sagittal sections are affine-transformed by affine transformer 80 on the basis of a view direction set by the parameters and then combined and displayed on monitor 82.
- This image is called "volume multi-plane reconstruction (MPR) image”. Note that since the view direction can be changed, the volume MPR image can be obtained from any angle.
- MPR volume multi-plane reconstruction
- cutting can be simulated.
- cutting portion 84 is designated by the ROI input.
- section extraction circuit 78 extracts sectional images of sagittal sections S1 and S2 and axial sections A1 and A2 including an edge of cutting portion 84 and coronal section C including a bottom (in a depth direction) of portion 84. These extracted sections are affine-transformed and combined, thereby displaying a volume MPR three-dimensional image as shown in FIG. 8C.
- FIG. 9 shows such multi-frame display.
- the upper right image is the volume MPR image
- the upper left, lower left, and lower right images are the axial, coronal, and sagittal sectional images, respectively.
- the surface image according to the first embodiment and the volume MPR image according to the second embodiment are combined in a multi-frame manner as shown in FIG. 10, three-dimensional images viewed from the same view point and having the same size can be observed at the same time. Therefore, a positional relationship between the bones, blood vessels, and veins can be easily recognized.
- the upper left image is the volume MPR image
- the upper right image is a surface image of the epidermis in a three-dimensional space of the volume MPR image
- the lower right image is a surface image of the blood vessels in the three-dimensional space.
- simulation display of the cutting portion is omitted, it can be performed. Display shown in FIG. 10 can be easily realized by combining the circuits of FIGS. 1 and 7.
- the surface image may be displayed together with the conventional oblique (section) image in a multi-frame manner.
- the section extraction circuit in FIG. 7 need only extract an oblique surface, and the oblique image is displayed instead of volume MPR image in FIG. 10.
- a coronal section including a bottom surface in a cutting depth direction may be displayed instead of the surface image within the cutting area, and sagittal and axial sections both contacting the coronal section may be combined in a view direction of the surface image, thereby combining and displaying the surface image and the volume MPR image as shown in FIG. 11.
- cutting can be simulated more easily.
- an oblique sectional image in the cutting area may be displayed instead of the volume MPR image in FIG. 11, thereby combining and displaying the surface and oblique images as shown in FIG. 12.
- a cutting portion can be three-dimensionally displayed in accordance with a cutting procedure
- a three-dimensional image processing apparatus which can perform simulation upon planning an operation.
Landscapes
- Physics & Mathematics (AREA)
- Engineering & Computer Science (AREA)
- General Physics & Mathematics (AREA)
- Theoretical Computer Science (AREA)
- Computer Graphics (AREA)
- Geometry (AREA)
- Software Systems (AREA)
- Apparatus For Radiation Diagnosis (AREA)
- Magnetic Resonance Imaging Apparatus (AREA)
- Analysing Materials By The Use Of Radiation (AREA)
- Image Generation (AREA)
Abstract
A three-dimensional image processing apparatus includes a first three-dimensional memory for storing first voxel data representing a three-dimensional CT image, a level detector for comparing the first voxel data with CT values of an epidermis, a bone, and a blood vessel, second three-dimensional memories for storing second voxel data (binary) of the epidermis, the bone, and the blood vessel obtained by the level detector, a distance detector for detecting distances between a predetermined projection plane in a three-dimensional space and the second voxel data, a minimum detector for detecting a distance between the projection plane and one of the second voxel data of the epidermis, bone, and blood vessel, which is closest to the projection plane, and a surface image generating circuit for shading minimum values of pixels in the projection plane to generate a surface image. The projection plane in the three-dimensional space is partially moved into a memory space in the second voxel data, thereby simulating a surface image obtained when a three-dimensional CT image is cut.
Description
The present invention relates to a three-dimensional image processing apparatus and, more particularly, to a three-dimensional image processing apparatus for displaying soft tissues (also called as parenchyma) of a human body such as an epidermis and a blood vessel.
Recently, three-dimensional image processing techniques using a CT (computed tomography) image and an MR (magnetic resonance) image have been widely developed.
In practice, three-dimensional image processing for bones (hard parts) has been realized in a clinical case. This is because an image of bones can be easily extracted. Bones appear on an X-ray CT image as a portion having a high CT value. Therefore, if a portion having a CT value larger than a predetermined threshold value is defined as a bone, binary display distinguishing between bones and other portions can be performed.
An example of a display method of soft tissues is a method of reconstructing a given section using a plurality of parallel CT images (sagittal, coronal, and oblique images). However, since each image is a section, positional relationship between the images cannot be easily recognized. As a result, it is difficult to allow three-dimensional recognition of the object.
In addition, a demand has recently arisen for three-dimensional simulation in planning an operation. Therefore, a surface image of a given portion of three-dimensional object must be displayed. However, since soft tissues cannot be easily three-dimensionally displayed, it is impossible to simulate an operation.
It is, therefore, an object of the present invention to provide a three-dimensional image processing apparatus which can three-dimensionally display an object without damaging its original information and hence can support simulation in planning an operation.
According to the three-dimensional image processing apparatus of the present invention, a plurality of second voxel data which represent three-dimensional objects of tissues is extracted from first voxel data which represents a three-dimensional object, a distance between a predetermined projection plane and each second voxel data in a three-dimensional space is obtained, and a surface image is formed in accordance with a distance of the second voxel data which is closest to the projection plane. Then, the projection plane is moved in the three-dimensional space close to a memory space of the second voxel data, thereby simulating a surface image obtained when the three-dimensional image is cut.
In addition, according to the three-dimensional image processing apparatus of the present invention, axial, sagittal, and coronal sectinal data are extracted from voxel data which represents a three-dimensional object. These sectional data are affine-transformed and combined on the basis of a view direction to form a volume multi-plane reconstruction (MPR) image. This volume MPR image is simply displayed or displayed in a multi-frame manner together with the axial, sagittal, and coronal sectional images.
Moreover, according to the three-dimensional image processing apparatus of the present invention, the above surface and volume MPR images are combined and displayed in a multi-frame manner.
FIG. 1 is a block diagram of a first embodiment of a three-dimensional image processing apparatus according to the present invention;
FIG. 2 is a perspective view of voxel data which represents a three dimensional object;
FIGS. 3A, 3B, and 3C are perspective views of voxel data of an epidermis, a bone, and a blood vessel extracted from the voxel data shown in FIG. 2;
FIG. 4 is a plan view of surface image according to the first embodiment which simulates cutting;
FIG. 5 is a schematic view for explaining distance data according to the first embodiment;
FIG. 6 is a flow chart of an operation of the first embodiment;
FIG. 7 is a block diagram of a second embodiment of the three-dimensional image processing apparatus according to the present invention;
FIGS. 8A, 8B, and 8C are perspective views showing an operation procedure of the second embodiment;
FIG. 9 is a plan view of multi-frame display as an example according to the second embodiment;
FIG. 10 is a plan view of multi-frame display combined of an image according to the first embodiment and that according to the second embodiment;
FIG. 11 is a perspective view of a combination display of a surface image and a volume multi-plane reconstruction image; and
FIG. 12 is a perspective view of a combination display of a surface image and an oblique image.
Embodiments of a three-dimensional image processing apparatus according to the present invention will be described below with reference to the accompanying drawings.
FIG. 1 is a block diagram of a first embodiment. A plurality of tomographic image data (multilevel data having a density gradation) acquired by an X-ray apparatus, an MRI (magnetic resonance imaging) apparatus, or the like is stored in three-dimensional memory 10 as voxel data. If resolution in a direction perpendicular to a slice (tomographic section) is poor in the actual tomographic image data, data between slices is obtained by interporation.
FIG. 2 shows such voxel data. In FIG. 2, voxel data concerns a head portion of a human body.
Read address generator 12 is connected to memory 10.
The output terminal of memory 10 is connected to level detector 14. Detector 14 has a plurality of ranges of CT value and binarizes an output from memory 10 in accordance with each range. This is, when the output from memory 10 has a value within a predetermined range, detector 14 supplies a signal of level "1". Otherwise, detector 14 supplies a signal of level "0". In this case, if ranges including CT values of an epidermis, a bone, and a blood vessel are used as predetermined ranges, binary voxel data of the epidermis, the bone, and the blood vessel can be written in three- dimensional memories 16a, 16b, and 16c as shown in FIGS. 3A, 3B, and 3C, respectively. Generator 12 is also connected to memories 16a 16b, and 16c.
Outputs from memories 16a, 16b, and 16c are supplied to distance detector 18. Detector 18 detects a distance from a projection plane to a three-dimensional object assuming that the three-dimensional object is projected from a given view point to the projection plane. For this purpose, parameters for defining the projection plane and a view direction (direction perpendicular to the projection plane) are input to detector 18. As parameters defining the projection plane, coordinates of two points on the diagonal line of the projection plane a distance between a center of the voxel and the projection plane, and the matrix size of the projection plane are input. As parameter defining the view direction, coordinates of two points on the line along the view direction are input.
FIG. 5 shows this distance. Assuming that a distance between projection plane 50 and predetermined plane 52 parallel to projection plane 50 is D, distance d from projection plane 50 to three-dimensional object 54 is detected. If distance D is known, distance d can be obtained by detecting longest distance D-d from plane 52 to object 54.
The distance from voxel data of each tissue to the projection plane is obtained to form a surface image of each tissue as will be described later.
Distances from the projection plane to the three-dimensional images respectively of the epidermis, the bone, and the blood vessel are input to Z-buffers 20a, 20b, and 20c. Outputs from Z-buffers 20a 20b, and 20c are supplied to minimum detector 22.
As a result, a distance from the projection plane to the surface of the three-dimensional object which is closest to the projection plane of the three-dimensional objects of the respective tissues is written in memory 24.
In this case, if the projection plane is located outside a memory space of voxel data, data of a distance to the epidermis is selected as a minimum distance. When the projection plane is moved closer to the memory space of the voxel data and finally enters the memory space, the distance data of the epidermis is excluded, and then distance data of the bone is excluded. Finally, a distance of the blood vessel image is selected as a minimum value.
For this reason, when part of the projection plane is sequentially moved closer to the memory space of the voxel data along a view direction (direction perpendicular to the projection plane), an interior of the head portion can be gradually seen as in an actual operation. This part of the projection plane corresponds to a cutting area and a moving distance corresponds to a cutting depth in an operation. For this reason, parameters representing the cutting area and the cutting depth (i.e., coordinates representing the cutting area and a length representing the cutting depth) are input to detector 22. Therefore, as for the pixels in the cutting area, the distance data is corrected assuming that the projection plane is shifted to the memory space of the voxel data by an amount of the cutting depth. That is, as for the pixels in the cutting area, after the cutting depth is subtracted from the outputs from Z-buffers 20a, 20b, and 20c, the minimum distance is detected. If a distance is obtained as a negative value upon subtraction, this distance is excluded from minimum distance detection assuming that a tissue represented by the distance is already removed by cutting.
Distance data output from memory 24 is supplied to surface image generator 28. Generator 28 performs shading of two-dimensional image data including the distance data to generate a surface image and displays the surface image which is partially cut as shown in FIG. 4 on monitor 30.
Write address generator 12, level detector 14, and memories 16a, 16b, and 16c constitute an extraction portion of images of the epidermis, the bone, and the blood vessel. Write address generator 26, distance detector 18, Z-buffers 20a, 20b, and 20c, and minimum detector 22 constitute a distance data formation portion.
When it is desired that the voxel data is modified by changing the view direction, the view direction parameter is changed and the same processing is repeated. In this case, the voxel data concerning the epidermis and the blood vessel which are excluded by cutting must be changed from "1" to "0" in memories 16a and 16b, respectively.
In the first embodiment, in order to select the three-dimensional image data which is closest to the projection plane, i.e., which is to be displayed as the surface image, a minimum value of distance d from the projection plane to a position at which data is "1" is obtained. However, when D-d shown in FIG. 5 is used as distance data I (z), a detector for detecting a maximum value of data I (z) may be provided instead of the minimum detector.
As described above, according to the first embodiment of the present invention, surface images of a variety of tissues (e.g., a bone, a blood vessel, and a tumor) can be displayed in a single three-dimensional space so that a positional relationship between the objects obtained when viewed from a predetermined projection plane is recognized well. In addition, since the projection plane can be partially moved closer to a tissue, tissues such as an epidermis, a bone, and a blood vessel can be sequentially displayed in the order named, thereby enabling simulation of an operation.
A flow chart of an operation of the first embodiment is shown in FIG. 6. In FIG. 6, step 62 is a step for obtaining distances from the projection plane to the respective voxel data in the cutting area; step 64 is a step for obtaining a minimum value of the distances to the respective three-dimensional images in the cutting area; and step 66 is a determination step for interactively performing this simulation. In this case, until a desired simulation image is obtained, steps 62 and 64 are repeated by changing a cutting area and a cutting depth. Steps 62 and 64 relate to a provisional cutting operation.
If YES in step 66, data concerning the cutting area and the cutting depth of data stored in three- dimensional memories 16a, 16b, and 16c are set to be 0 in real cutting step 68. Therefore, voxel data of each tissue can be removed in accordance with cutting. Thereafter, in step 70, the data in memories 16a, 16b, and 16c are subjected to handling processing (rotation and parallel movement) to change the view direction.
A second embodiment of the present invention will be described below.
As shown in FIG. 7, an output from three-dimentional memory 74 is supplied to section extraction circuit 78 through interpolation circuit 76. As in the first embodiment, voxel data is written in memory 74. Interpolation circuit 76 interpolates data between slices. Section extraction circuit 78 extracts sectional data of axial, coronal, and sagittal sections from the voxel data.
A relationship between the axial, coronal, and sagittal sections is shown in FIG. 8A.
Parameters for specifying positions of the respective sections are input by an ROI (region of interest) input such as a tracker ball.
The sectional data of the axial, coronal, and sagittal sections are affine-transformed by affine transformer 80 on the basis of a view direction set by the parameters and then combined and displayed on monitor 82. This image is called "volume multi-plane reconstruction (MPR) image". Note that since the view direction can be changed, the volume MPR image can be obtained from any angle.
In the second embodiment, cutting can be simulated. As shown in FIG. 8B, cutting portion 84 is designated by the ROI input. Then, section extraction circuit 78 extracts sectional images of sagittal sections S1 and S2 and axial sections A1 and A2 including an edge of cutting portion 84 and coronal section C including a bottom (in a depth direction) of portion 84. These extracted sections are affine-transformed and combined, thereby displaying a volume MPR three-dimensional image as shown in FIG. 8C.
However, according to the above volume MPR image, although a positional relationship between the respective sections can be recognized, an actual size cannot be known. Therefore, it is effective to display the volume MPR image together with the axial, coronal, and sagittal sectional images in a multi-frame manner. FIG. 9 shows such multi-frame display. In FIG. 9, the upper right image is the volume MPR image, and the upper left, lower left, and lower right images are the axial, coronal, and sagittal sectional images, respectively. With these images, each section can be observed in detail, and a positional relationship between the respective sections can be easily recognized. Note that a cutting portion is also displayed in each sectional image. In this case, as for a portion which is not seen, only lines indicating a section are displayed.
When the surface image according to the first embodiment and the volume MPR image according to the second embodiment are combined in a multi-frame manner as shown in FIG. 10, three-dimensional images viewed from the same view point and having the same size can be observed at the same time. Therefore, a positional relationship between the bones, blood vessels, and veins can be easily recognized. In FIG. 10, the upper left image is the volume MPR image, the upper right image is a surface image of the epidermis in a three-dimensional space of the volume MPR image, and the lower right image is a surface image of the blood vessels in the three-dimensional space. In FIG. 10, although simulation display of the cutting portion is omitted, it can be performed. Display shown in FIG. 10 can be easily realized by combining the circuits of FIGS. 1 and 7.
The surface image may be displayed together with the conventional oblique (section) image in a multi-frame manner. In this case, the section extraction circuit in FIG. 7 need only extract an oblique surface, and the oblique image is displayed instead of volume MPR image in FIG. 10.
In the surface image display according to the first embodiment of the present invention, a coronal section including a bottom surface in a cutting depth direction may be displayed instead of the surface image within the cutting area, and sagittal and axial sections both contacting the coronal section may be combined in a view direction of the surface image, thereby combining and displaying the surface image and the volume MPR image as shown in FIG. 11. As a result, cutting can be simulated more easily.
In addition, an oblique sectional image in the cutting area may be displayed instead of the volume MPR image in FIG. 11, thereby combining and displaying the surface and oblique images as shown in FIG. 12.
As has been described above, according to the present invention, since a cutting portion can be three-dimensionally displayed in accordance with a cutting procedure, there is provided a three-dimensional image processing apparatus which can perform simulation upon planning an operation.
Claims (10)
1. A three-dimensional image processing apparatus comprising:
memory means for storing first voxel data representing an object in a three-dimensional space;
extracting means for extracting a plurality of second voxel data representing a plurality of tissues from the first voxel data stored in said memory means;
first designating means for designating a predetermined plane in the three-dimensional space as a projection plane;
distance detecting means for detecting distances between pixels in the projection plane and voxels in each of said plurality of second voxel data;
second designating means for designating a predetermined range in the projection plane as a cutting area;
third designating means for designating a cutting depth in the cutting area;
distance correcting means for correcting the distances detected by said distance detecting means in accordance with the cutting depth;
minimum distance detecting means for detecting a minimum value of the distances between the pixels in the projection plane and the voxels in each of said plurality of second voxel data; and
surface image generating means for generating a surface image in accordance with the minimum value of the distances of the pixels in the projection plane obtained by said minimum distance detecting means.
2. An apparatus according to claim 1, further comprising simulating means for simulating cutting of the object in the three-dimensional space by changing a position of the projection plane, a size of the cutting area, and the cutting depth.
3. An apparatus according to claim 1, in which said distance correcting means corrects the distances by subtracting the cutting depth from the distances detected by said distance detecting means.
4. An apparatus according to claim 1, in which said extracting means compares the first voxel data with specific threshold values of a plurality of tissues and forms a plurality of binary second voxel data.
5. A three-dimensional image processing apparatus comprising:
memory means for storing voxel data representing a three-dimensional object;
extracting means for extracting sectional data representing axial, coronal, and sagittal images from the voxel data stored in said memory means; and
means for affine-transforming the sectional data extracted by said extracting means and three-dimensionally combining the affine-transformed sectional data based on a view direction, thereby generating a volume multi-plane reconstruction image.
6. An apparatus according to claim 5, in which said extracting means comprises:
designating means for designating a cutting area and a cutting depth; and
means for extracting a section including an edge of the cutting area and a section located at the cutting depth.
7. An apparatus according to claim 5, further comprising display means for displaying the volume multi-plane reconstruction image and the axial, coronal, and sagit-tal sectional images in a multi-frame manner.
8. A three-dimensional image processing apparatus comprising:
memory means for storing first voxel data representing an object in a three-dimensional space;
first extracting means for extracting a plurality of second voxel data representing three-dimensional objects of a plurality of tissues from the first voxel data stored in said memory means;
designating means for designating a predetermined plane in the three-dimensional space as a projection plane;
distance detecting means for detecting distances between pixels in the projection plane and voxels in each of said plurality of second voxel data;
surface image generating means for generating surface images of the second voxel data in accordance with the distances of the pixels obtained by said distance detecting means;
second extracting means for extracting sectional data representing axial, coronal, sagittal images from the first voxel data stored in said memory means;
volume multi-plane reconstruction image generating means for affine-transforming the sectional data extracted by said second extracting means and three-dimensionally combining the affine-transformed sectional data based on a view direction, thereby generating a volume multi-plane reconstruction image; and
display means for displaying the surface images of the second voxel data and the volume multi-plane reconstruction image in a multi-frame manner. .Iadd.9. A three-dimensional image processing apparatus comprising:
memory means for storing first voxel data representing an object in a three-dimensional space, the first voxel data comprising multilevel data;
extracting means for extracting a plurality of second voxel data representing a plurality of tissues from the first voxel data stored in said memory means, the second voxel data comprising binary data;
first designating means for designating a predetermined plane in the three-dimensional space as a projection plane;
distance detecting means for detecting distances between pixels in the projection plane and voxels in each of said plurality of second voxel data;
second designating means for designating a predetermined range in the projection plane as a cutting area;
third designating means for designating a cutting depth in the cutting area;
distance correcting means for correcting the distances detected by said distance detecting means in accordance with the cutting depth;
minimum distance detecting means for detecting a minimum value of the distances between the pixels in the projection plane and the voxels in each of said plurality of second voxel data, the distances having been corrected by the distance correcting means; and
surface image generating means for generating a surface image in accordance with the minimum value of the distances of the pixels in the projection plane obtained by said minimum distance detecting means.
.Iaddend..Iadd. An apparatus according to claim 9, further comprising simulating means for simulating cutting of the object in the three-dimensional space by changing a position of the projection plane, a size of the cutting area, and the cutting depth. .Iaddend..Iadd.11. An apparatus according to claim 9, in which said distance correcting means corrects the distances by subtracting the cutting depth from the distances
detected by said distance detecting means. .Iaddend..Iadd.12. An apparatus according to claim 9, in which said extracting means compares the first voxel data with specific threshold values of a plurality of tissues and forms a plurality of binary second voxel data. .Iaddend..Iadd.13. A three-dimensional image processing apparatus comprising:
memory means for storing first voxel data representing an object in a three-dimensional space, the first voxel data comprising multilevel data;
first extracting means for extracting a plurality of second voxel data representing three-dimensional objects from a plurality of tissues from the first voxel data stored in said memory means, the second voxel data comprising binary data;
designating means for designating a predetermined plane in the three-dimensional space as a projection plane;
distance detecting means for detecting distances between pixels in the projection plane and voxels in each of said plurality of second voxel data;
surface image generating means for generating surface images of the second voxel data in accordance with the distances of the pixels obtained by said distance detecting means;
second extracting means for extracting sectional data representing axial, coronal, sagittal images from the first voxel data stored in said memory means;
volume multi-plane reconstruction image generating means for affine-transforming the sectional data extracted by said second extracting means and three-dimensionally combining the affine-transformed sectional data based on a view direction, thereby generating a volume multi-plane reconstruction image; and
display means for displaying the surface images of the second voxel data and the volume multi-plane reconstruction image in a multi-frame manner. .Iaddend.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US08/547,152 USRE35798E (en) | 1987-01-28 | 1995-10-24 | Three-dimensional image processing apparatus |
Applications Claiming Priority (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP62016024A JP2563298B2 (en) | 1987-01-28 | 1987-01-28 | Three-dimensional image processing device |
JP62-16024 | 1987-01-28 | ||
US07/147,495 US4835688A (en) | 1987-01-28 | 1988-01-26 | Three-dimensional image processing apparatus |
US08/547,152 USRE35798E (en) | 1987-01-28 | 1995-10-24 | Three-dimensional image processing apparatus |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US07/147,495 Reissue US4835688A (en) | 1987-01-28 | 1988-01-26 | Three-dimensional image processing apparatus |
Publications (1)
Publication Number | Publication Date |
---|---|
USRE35798E true USRE35798E (en) | 1998-05-19 |
Family
ID=11904994
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US07/147,495 Ceased US4835688A (en) | 1987-01-28 | 1988-01-26 | Three-dimensional image processing apparatus |
US08/547,152 Expired - Lifetime USRE35798E (en) | 1987-01-28 | 1995-10-24 | Three-dimensional image processing apparatus |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US07/147,495 Ceased US4835688A (en) | 1987-01-28 | 1988-01-26 | Three-dimensional image processing apparatus |
Country Status (2)
Country | Link |
---|---|
US (2) | US4835688A (en) |
JP (1) | JP2563298B2 (en) |
Cited By (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6219059B1 (en) | 1996-10-16 | 2001-04-17 | Vital Images, Inc. | Interactive control of voxel attributes using selectable characteristics |
US6507632B1 (en) | 2001-10-16 | 2003-01-14 | Ge Medical Systems Global Technology Company, Llc | Method and apparatus for reducing artifacts in an image |
US20030014400A1 (en) * | 2001-06-12 | 2003-01-16 | Advanced Research And Technology Institute | System and method for case study instruction |
US6867808B1 (en) | 1999-03-19 | 2005-03-15 | Scott T. Boden | Time domain imager |
US6891963B1 (en) * | 1999-01-06 | 2005-05-10 | Hitachi Medical Corporation | Image display |
US20060181527A1 (en) * | 2005-02-11 | 2006-08-17 | England James N | Method and apparatus for specifying and displaying measurements within a 3D rangefinder data set |
US20060182314A1 (en) * | 2005-02-11 | 2006-08-17 | England James N | Method and apparatus for displaying a calculated geometric entity within one or more 3D rangefinder data sets |
US7242402B1 (en) * | 1999-06-21 | 2007-07-10 | G.E. Medical Systems, S.A. | Method of visualization of a part of a three-dimensional image |
US20090135993A1 (en) * | 2007-11-27 | 2009-05-28 | Siemens Aktiengesellschaft | Computed tomography method |
US9091628B2 (en) | 2012-12-21 | 2015-07-28 | L-3 Communications Security And Detection Systems, Inc. | 3D mapping with two orthogonal imaging views |
Families Citing this family (56)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5309356A (en) * | 1987-09-29 | 1994-05-03 | Kabushiki Kaisha Toshiba | Three-dimensional reprojected image forming apparatus |
US4984157A (en) * | 1988-09-21 | 1991-01-08 | General Electric Company | System and method for displaying oblique planar cross sections of a solid body using tri-linear interpolation to determine pixel position dataes |
US4953087A (en) * | 1988-10-24 | 1990-08-28 | General Electric Company | Three-dimensional images obtained from tomographic data having unequally spaced slices |
US5113357A (en) * | 1989-05-18 | 1992-05-12 | Sun Microsystems, Inc. | Method and apparatus for rendering of geometric volumes |
JP2931983B2 (en) * | 1989-06-30 | 1999-08-09 | ジーイー横河メディカルシステム株式会社 | Radiation therapy system |
JP2714164B2 (en) * | 1989-07-31 | 1998-02-16 | 株式会社東芝 | 3D image display |
JP2845995B2 (en) * | 1989-10-27 | 1999-01-13 | 株式会社日立製作所 | Region extraction method |
US5127037A (en) * | 1990-08-15 | 1992-06-30 | Bynum David K | Apparatus for forming a three-dimensional reproduction of an object from laminations |
US5475613A (en) * | 1991-04-19 | 1995-12-12 | Kawasaki Jukogyo Kabushiki Kaisha | Ultrasonic defect testing method and apparatus |
US5555352A (en) * | 1991-04-23 | 1996-09-10 | International Business Machines Corporation | Object-based irregular-grid volume rendering |
US5301117A (en) * | 1991-10-30 | 1994-04-05 | Giorgio Riga | Method for creating a three-dimensional corporeal model from a very small original |
US5734384A (en) * | 1991-11-29 | 1998-03-31 | Picker International, Inc. | Cross-referenced sectioning and reprojection of diagnostic image volumes |
US5428716A (en) * | 1991-12-26 | 1995-06-27 | International Business Machines Corporation | Solid-clip methodology and architecture for clipping solid models and displaying cross-sections using depth-buffers |
US5603318A (en) | 1992-04-21 | 1997-02-18 | University Of Utah Research Foundation | Apparatus and method for photogrammetric surgical localization |
US5566279A (en) * | 1993-05-17 | 1996-10-15 | Nec Corporation | Method of and apparatus for reading out digital image data from three-dimensional memory |
US5396890A (en) * | 1993-09-30 | 1995-03-14 | Siemens Medical Systems, Inc. | Three-dimensional scan converter for ultrasound imaging |
JPH07234927A (en) * | 1994-02-22 | 1995-09-05 | Toshiba Medical Eng Co Ltd | Three-dimensional image display device |
JP3480608B2 (en) * | 1994-11-07 | 2003-12-22 | 株式会社日立メディコ | Projection image creation method and apparatus therefor |
JP3203160B2 (en) * | 1995-08-09 | 2001-08-27 | 三菱電機株式会社 | Volume rendering apparatus and method |
US6226418B1 (en) | 1997-11-07 | 2001-05-01 | Washington University | Rapid convolution based large deformation image matching via landmark and volume imagery |
US6408107B1 (en) | 1996-07-10 | 2002-06-18 | Michael I. Miller | Rapid convolution based large deformation image matching via landmark and volume imagery |
US6340353B1 (en) * | 1996-09-30 | 2002-01-22 | Jeanne K. Pomatto | Manufacture of cranial remodeling orthosis |
EP0931420A4 (en) * | 1996-10-11 | 2002-06-26 | Sarnoff Corp | Stereoscopic video coding and decoding apparatus and method |
JPH10124649A (en) * | 1996-10-21 | 1998-05-15 | Toshiba Iyou Syst Eng Kk | Mpr image preparing device |
US6075871A (en) * | 1998-02-11 | 2000-06-13 | Analogic Corporation | Apparatus and method for eroding objects in computed tomography data |
US6067366A (en) * | 1998-02-11 | 2000-05-23 | Analogic Corporation | Apparatus and method for detecting objects in computed tomography data using erosion and dilation of objects |
US6272230B1 (en) | 1998-02-11 | 2001-08-07 | Analogic Corporation | Apparatus and method for optimizing detection of objects in computed tomography data |
EP1062555A4 (en) * | 1998-02-11 | 2001-05-23 | Analogic Corp | Computed tomography apparatus and method for classifying objects |
US6078642A (en) * | 1998-02-11 | 2000-06-20 | Analogice Corporation | Apparatus and method for density discrimination of objects in computed tomography data using multiple density ranges |
US6076400A (en) * | 1998-02-11 | 2000-06-20 | Analogic Corporation | Apparatus and method for classifying objects in computed tomography data using density dependent mass thresholds |
US6128365A (en) * | 1998-02-11 | 2000-10-03 | Analogic Corporation | Apparatus and method for combining related objects in computed tomography data |
US6317509B1 (en) | 1998-02-11 | 2001-11-13 | Analogic Corporation | Computed tomography apparatus and method for classifying objects |
US6111974A (en) * | 1998-02-11 | 2000-08-29 | Analogic Corporation | Apparatus and method for detecting sheet objects in computed tomography data |
US6026171A (en) * | 1998-02-11 | 2000-02-15 | Analogic Corporation | Apparatus and method for detection of liquids in computed tomography data |
US6026143A (en) * | 1998-02-11 | 2000-02-15 | Analogic Corporation | Apparatus and method for detecting sheet objects in computed tomography data |
US6035014A (en) * | 1998-02-11 | 2000-03-07 | Analogic Corporation | Multiple-stage apparatus and method for detecting objects in computed tomography data |
US6396939B1 (en) | 1998-05-28 | 2002-05-28 | Orthosoft Inc. | Method and system for segmentation of medical images |
US6633686B1 (en) | 1998-11-05 | 2003-10-14 | Washington University | Method and apparatus for image registration using large deformation diffeomorphisms on a sphere |
US6718192B1 (en) | 1999-11-24 | 2004-04-06 | Ge Medical Systems Global Technology Company, Llc | Method and apparatus for real-time 3D image rendering on a picture archival and communications system (PACS) workstation |
US7013032B1 (en) * | 1999-11-24 | 2006-03-14 | The General Electric Company | Method and apparatus for secondary capture of 3D based images on a picture archival and communications (PACS) system |
JP2004517408A (en) * | 2000-12-22 | 2004-06-10 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | Stereoscopic viewing of the area between clipping planes |
US6844884B2 (en) * | 2000-12-27 | 2005-01-18 | Ge Medical Systems Global Technology Company, Llc | Multi-plane graphic prescription interface and method |
US7432924B2 (en) * | 2003-08-28 | 2008-10-07 | Kabushiki Kaisha Toshiba | 3D digital subtraction angiography image processing apparatus |
US7668285B2 (en) * | 2004-02-16 | 2010-02-23 | Kabushiki Kaisha Toshiba | X-ray computed tomographic apparatus and image processing apparatus |
JP5586953B2 (en) * | 2006-09-29 | 2014-09-10 | コーニンクレッカ フィリップス エヌ ヴェ | Access to medical image database using anatomical shape information |
JP5188693B2 (en) * | 2006-10-13 | 2013-04-24 | 富士フイルム株式会社 | Image processing device |
JP4636338B2 (en) * | 2007-03-28 | 2011-02-23 | ソニー株式会社 | Surface extraction method, surface extraction apparatus and program |
US8285014B2 (en) * | 2007-04-06 | 2012-10-09 | Siemens Aktiengesellschaft | Measuring blood volume with C-arm computed tomography |
CN103764038A (en) | 2012-02-21 | 2014-04-30 | 株式会社东芝 | X-ray CT device, image display device, and image display method |
US9734129B2 (en) * | 2014-04-22 | 2017-08-15 | Sandisk Technologies Llc | Low complexity partial parallel architectures for Fourier transform and inverse Fourier transform over subfields of a finite field |
US9432055B2 (en) | 2014-06-26 | 2016-08-30 | Sandisk Technologies Llc | Encoder for quasi-cyclic low-density parity-check codes over subfields using fourier transform |
US9444493B2 (en) | 2014-06-26 | 2016-09-13 | Sandisk Technologies Llc | Encoder with transform architecture for LDPC codes over subfields using message mapping |
US20170092013A1 (en) * | 2015-09-26 | 2017-03-30 | Boston Scientific Scimed Inc. | Adjustable depth anatomical shell editing |
CN105261052B (en) * | 2015-11-03 | 2018-09-18 | 沈阳东软医疗系统有限公司 | Method for drafting and device is unfolded in lumen image |
US10067071B2 (en) * | 2016-04-08 | 2018-09-04 | Flir Systems, Inc. | Analyte spatial detection systems and methods |
CN111803111B (en) * | 2020-07-20 | 2021-09-07 | 上海市第六人民医院 | Brain blood vessel display device and method |
Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4131021A (en) * | 1976-03-04 | 1978-12-26 | Rca Corporation | High resolution pulse-echo ultrasonic-imaging display system |
US4630203A (en) * | 1983-12-27 | 1986-12-16 | Thomas Szirtes | Contour radiography: a system for determining 3-dimensional contours of an object from its 2-dimensional images |
US4631750A (en) * | 1980-04-11 | 1986-12-23 | Ampex Corporation | Method and system for spacially transforming images |
US4751643A (en) * | 1986-08-04 | 1988-06-14 | General Electric Company | Method and apparatus for determining connected substructures within a body |
Family Cites Families (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS5962036A (en) * | 1982-09-30 | 1984-04-09 | 富士通株式会社 | Three-dimensional data display and treating system |
JPS5960678A (en) * | 1982-09-30 | 1984-04-06 | Fujitsu Ltd | Three-dimensional display system |
JPS61187083A (en) * | 1985-02-14 | 1986-08-20 | Hitachi Ltd | Storage device of picture element information |
JPS61206082A (en) * | 1985-03-11 | 1986-09-12 | Hitachi Ltd | Part deleting control circuit |
-
1987
- 1987-01-28 JP JP62016024A patent/JP2563298B2/en not_active Expired - Fee Related
-
1988
- 1988-01-26 US US07/147,495 patent/US4835688A/en not_active Ceased
-
1995
- 1995-10-24 US US08/547,152 patent/USRE35798E/en not_active Expired - Lifetime
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4131021A (en) * | 1976-03-04 | 1978-12-26 | Rca Corporation | High resolution pulse-echo ultrasonic-imaging display system |
US4631750A (en) * | 1980-04-11 | 1986-12-23 | Ampex Corporation | Method and system for spacially transforming images |
US4630203A (en) * | 1983-12-27 | 1986-12-16 | Thomas Szirtes | Contour radiography: a system for determining 3-dimensional contours of an object from its 2-dimensional images |
US4751643A (en) * | 1986-08-04 | 1988-06-14 | General Electric Company | Method and apparatus for determining connected substructures within a body |
Cited By (15)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6219059B1 (en) | 1996-10-16 | 2001-04-17 | Vital Images, Inc. | Interactive control of voxel attributes using selectable characteristics |
US6891963B1 (en) * | 1999-01-06 | 2005-05-10 | Hitachi Medical Corporation | Image display |
US6867808B1 (en) | 1999-03-19 | 2005-03-15 | Scott T. Boden | Time domain imager |
US7242402B1 (en) * | 1999-06-21 | 2007-07-10 | G.E. Medical Systems, S.A. | Method of visualization of a part of a three-dimensional image |
US20030014400A1 (en) * | 2001-06-12 | 2003-01-16 | Advanced Research And Technology Institute | System and method for case study instruction |
US6507632B1 (en) | 2001-10-16 | 2003-01-14 | Ge Medical Systems Global Technology Company, Llc | Method and apparatus for reducing artifacts in an image |
US20060182314A1 (en) * | 2005-02-11 | 2006-08-17 | England James N | Method and apparatus for displaying a calculated geometric entity within one or more 3D rangefinder data sets |
US20060181527A1 (en) * | 2005-02-11 | 2006-08-17 | England James N | Method and apparatus for specifying and displaying measurements within a 3D rangefinder data set |
US7777761B2 (en) | 2005-02-11 | 2010-08-17 | Deltasphere, Inc. | Method and apparatus for specifying and displaying measurements within a 3D rangefinder data set |
US7974461B2 (en) * | 2005-02-11 | 2011-07-05 | Deltasphere, Inc. | Method and apparatus for displaying a calculated geometric entity within one or more 3D rangefinder data sets |
US20110255749A1 (en) * | 2005-02-11 | 2011-10-20 | England James N | Method and apparatus for displaying a calculated geometric entity within one or more 3d rangefinder data sets |
US8879825B2 (en) * | 2005-02-11 | 2014-11-04 | Deltasphere, Inc. | Method and apparatus for displaying a calculated geometric entity within one or more 3D rangefinder data sets |
US20090135993A1 (en) * | 2007-11-27 | 2009-05-28 | Siemens Aktiengesellschaft | Computed tomography method |
US7916829B2 (en) * | 2007-11-27 | 2011-03-29 | Siemens Aktiengesellschaft | Computed tomography method |
US9091628B2 (en) | 2012-12-21 | 2015-07-28 | L-3 Communications Security And Detection Systems, Inc. | 3D mapping with two orthogonal imaging views |
Also Published As
Publication number | Publication date |
---|---|
JP2563298B2 (en) | 1996-12-11 |
JPS63186628A (en) | 1988-08-02 |
US4835688A (en) | 1989-05-30 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
USRE35798E (en) | Three-dimensional image processing apparatus | |
US5166876A (en) | System and method for detecting internal structures contained within the interior region of a solid object | |
US4914589A (en) | Three-dimensional images obtained from tomographic data using a variable threshold | |
US5412563A (en) | Gradient image segmentation method | |
US7356367B2 (en) | Computer aided treatment planning and visualization with image registration and fusion | |
US4989142A (en) | Three-dimensional images obtained from tomographic slices with gantry tilt | |
US4821213A (en) | System for the simultaneous display of two or more internal surfaces within a solid object | |
US4903202A (en) | Three-dimensional object removal via connectivity | |
US6055326A (en) | Method for orienting electronic medical images | |
US20040165766A1 (en) | Method and apparatus for forming and displaying projection image from a plurality of sectional images | |
US9563978B2 (en) | Image generation apparatus, method, and medium with image generation program recorded thereon | |
Kim et al. | Automatic extraction of inferior alveolar nerve canal using feature-enhancing panoramic volume rendering | |
US4953087A (en) | Three-dimensional images obtained from tomographic data having unequally spaced slices | |
JPS6237782A (en) | Apparatus and method for displaying 3-d surface structure | |
CN112862833A (en) | Blood vessel segmentation method, electronic device and storage medium | |
US20040161144A1 (en) | Method for producing an image | |
CN111932665A (en) | Hepatic vessel three-dimensional reconstruction and visualization method based on vessel tubular model | |
US6522324B1 (en) | Deriving an iso-surface in a multi-dimensional data field | |
JP4010034B2 (en) | Image creation device | |
EP0373854B1 (en) | Apparatus and method for detecting internal structures contained within the interior region of a solid object | |
Rusinek et al. | Quantitative and qualitative comparison of volumetric and surface rendering techniques | |
EP0354026B1 (en) | Three-dimensional display of tomographic data | |
CN115035070A (en) | Method and device for determining position of implant in CBCT image | |
JPH0728976A (en) | Picture display device | |
CN115908225A (en) | Tubular organ labeling method, tubular organ labeling result correction method and tubular organ labeling result correction system |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
FPAY | Fee payment |
Year of fee payment: 12 |