Abstract:
A method and systems for obtaining 2D ultrasound images. The methods may comprise the steps of receiving ultrasonic information from a volumetric region of a body, volume scan converting the ultrasonic information from the volumetric region for processing a rendering box, and volume rendering the rendering box for projecting the rendering box onto a 2D slice by using volume rendering techniques. The systems may comprise an ultrasonic transducer for receiving ultrasonic information from a volumetric region of a body, a volume scan converter for processing a rendering box obtained from the volumetric region, and a volume rendering processor for projecting the rendering box onto a 2D slice by using volume rendering techniques for contrast enhancement.

Description:
BACKGROUND OF THE INVENTION 
     Embodiments of the present invention are directed generally to ultrasonic imaging. More particularly, various embodiments of the present invention are directed to apparatus and methods for generating 2D images from multiple 2D slices at different spatial locations. 
     Conventional 2D ultrasound scanners produce a two-dimensional slice by using a transducer to transmit ultrasonic pulses and receive echoes from structures inside a body. While the transducer is held in one position, pulses are fired to multiple points throughout a 2D scan area. The scan area is formed in a single plane and has a very thin thickness. The echo information is then displayed as a planar image made up of 2D pixels. The displayed information depends on specific properties of the transducer such as frequency, focal range, and axial and lateral resolution. While certain properties of the transducer can be varied (e.g., transmission frequency, receive frequency), it remains desirable to improve image quality by improving tissue contrast in conventional 2D images. Thus, there is a need for methods and apparatus of ultrasound imaging that continue to improve tissue contrast. 
     Two conventional methods of contrast enhancement concern filtering and utilizing a dynamic window. The filtering and windowing methods may decrease the amount of information in the image because of the presence of speckle. Thus, there is a need for methods and apparatus of ultrasound imaging that improve tissue contrast by reducing speckle. 
     BRIEF SUMMARY OF THE INVENTION 
     In accordance with one embodiment of the present invention, a medical diagnostic ultrasound system for developing a 2D image having contrast enhancement comprises an ultrasonic transducer for receiving ultrasonic information from a volumetric region of a body, memory storing adjacent image lines or planes formed from received ultrasonic information from the volumetric region, a rendering box control module defining a thickness of a rendering box overlapping a portion of the adjacent image lines or planes, and a volume rendering processor for combining and projecting portions of image lines or planes within the rendering box onto a 2D image based on volume rendering techniques that enhance contrast. 
     The ultrasonic transducer may be a 3D transducer or a 2D matrix array. The system may further comprise a volume scan converter that generates the image lines or planes based on geometric information that calculates a position of neighboring ultrasonic information to derive voxel data. The volume rendering processor may project the portion of the image lines or planes in the rendering box in real-time. The system may further comprise memory for storing the ultrasonic information before being scan converted to form the image lines or planes. The volume rendering processor may employ algorithms for surface texture and maximum transparency. The volume rendering processor may perform at least one of the following operations upon the image lines or planes: surface texture, maximum transparency, transparent minimum, and gradient light rendering. The transducer may operate in at least one of the following acquisition modes: conventional grayscale sonography, 2D compound imaging, color Doppler, and duplex sonography with spectral Doppler. The transducer may receive tissue harmonic imaging information. The transducer may receive pulse inversion harmonic imaging information. 
     Certain embodiments of the present invention comprise a method for developing a 2D image representation for image contrast enhancement in a medical diagnostic ultrasound system comprising the steps of: receiving ultrasonic information from a volumetric region of a body, storing adjacent image lines or planes formed from received ultrasonic information from the volumetric region, forming a rendering box overlapping a portion of the adjacent image lines or planes and having a thickness, and volume rendering the rendering box for combining and projecting portions of image lines or planes within the rendering box onto a 2D image based on volume rendering techniques that enhance contrast. 
     The step of receiving ultrasonic information may be performed by a 3D transducer or a 2D matrix array. The method may further comprise a step of volume scan converting that generates the image lines or planes based on geometric information that calculates a position of neighboring ultrasonic information to derive voxel data. The step of volume rendering may project the portion of the image lines or planes in the rendering box in real-time. The method may further comprise a step of storing the ultrasonic information before being scan converted to form the image lines or planes. The step of volume rendering may perform at least one of the following operations upon the image lines or planes: surface texture, maximum transparency, transparent minimum, and gradient light rendering. The step of receiving ultrasonic information may employ at least one of the following acquisition modes: conventional grayscale sonography, 2D compound imaging, color Doppler, and duplex sonography with spectral Doppler. The step of receiving ultrasonic information may comprise receiving tissue harmonic imaging information. The step of receiving ultrasonic information may comprise receiving pulse inversion harmonic imaging information. 
    
    
     BRIEF DESCRIPTION OF THE DRAWINGS 
     The foregoing summary, as well as the following detailed description of the preferred embodiments of the present invention, will be better understood when read in conjunction with the appended drawings. For the purpose of illustrating the preferred embodiments of the present invention, there is shown in the drawings, embodiments which are presently preferred. It should be understood, however, that the present invention is not limited to the arrangements and instrumentality shown in the attached drawings. 
     FIG. 1 is a block diagram of an apparatus formed in accordance with one embodiment of the present invention. 
     FIG. 2 is an isometric drawing of a rendering box formed in accordance with one embodiment of the present invention. 
     FIG. 3 is a schematic of an ultrasound display that displays an example of an embodiment of volume rendering imaging in accordance with one embodiment of the present invention. 
     FIG. 4 is a diagram illustrating a split screen display in accordance with an embodiment of the present invention. 
    
    
     DETAILED DESCRIPTION OF THE INVENTION 
     FIG. 1 illustrates an ultrasound system formed in accordance with one embodiment of the present invention. The system includes a probe  10  connected to a transmitter  12  and a receiver  14 . The probe  10  transmits ultrasonic pulses and receives echoes from structures inside of a scanned ultrasound volume  16 . Memory  20  stores ultrasound data from the receiver  14  derived from the scanned ultrasound volume  16 . The volume  16  may be obtained by various techniques (e.g., 3D scanning, real-time 3D imaging, volume scanning, 2D scanning with transducers having positioning sensors, freehand scanning using a Voxel correlation technique, 2D or matrix array transducers and the like). 
     The transducer  10  is moved, such as along a linear or arcuate path, while scanning a region of interest (ROI). At each linear or arcuate position, the transducer  10  obtains scan planes  18 . The scan planes  18  are collected for a thickness, such as from a group or set of adjacent scan planes  18 . The scan planes  18  are stored in the memory  20 , and then passed to a volume scan converter  42 . In some embodiments, the transducer  10  may obtain lines instead of the scan planes  18 , and the memory  20  may store lines obtained by the transducer  10  rather than the scan planes  18 . The volume scan converter  42  receives a slice thickness setting from a control input  40 , which identifies the thickness of a slice to be created from the scan planes  18 . The volume scan converter  42  creates a data slice from multiple adjacent scan planes  18 . The number of adjacent scan planes  18  that are combined to form each data slice is dependent upon the thickness selected by slice thickness control input  40 . The data slice is stored in slice memory  44  and is accessed by a volume rendering processor  46 . The volume rendering processor  46  performs volume rendering upon the data slice. The output of the volume rendering processor  46  is passed to the video processor  50  and display  67 . 
     The position of each echo signal sample (Voxel) is defined in terms of geometrical accuracy (i.e., the distance from one Voxel neighbor to the next) and ultrasonic response (and derived values from the ultrasonic response). Suitable ultrasonic responses include gray scale values, color flow values, and angio or power Doppler information. 
     FIG. 2 illustrates a real-time 4D volume  16  acquired by the system of FIG. 1 in accordance with one embodiment. The volume  16  includes a sector shaped cross-section with radial borders  22  and  24  diverging from one another at angle  26 . The probe  10  electronically focuses and directs ultrasound firings longitudinally to scan along adjacent scan lines in each scan plane  18  and electronically or mechanically focuses and directs ultrasound firings laterally to scan adjacent scan planes  18 . Scan planes  18  obtained by the probe  10 , as illustrated in FIG. 1, are stored in memory  20  and are scan converted from spherical to Cartesian coordinates by the volume scan converter  42 . A volume comprising multiple scan planes is output from the volume scan converter  42  and stored in the slice memory  44  as rendering box  30  (FIG.  2 ). The rendering box  30  in the slice memory  44  is formed from multiple adjacent image planes  34 . 
     The rendering box  30  may be defined in size by an operator to have a slice thickness  32 , width  36  and height  38 . The volume scan converter  42  may be controlled by the slice thickness control input  40  to adjust the thickness parameter of the slice to form a rendering box  30  of the desired thickness. The rendering box  30  designates the portion of the scanned volume  16  that is volume rendered. The volume rendering processor  46  accesses the slice memory  44  and renders along the thickness  32  of the rendering box  30 . 
     During operation, a 3D slice having a pre-defined, substantially constant thickness (also referred to as the rendering box  30 ) is acquired by the slice thickness setting control  40  (FIG. 1) and is processed in the volume scan converter  42  (FIG.  1 ). The echo data representing the rendering box  30  may be stored in slice memory  44 . Predefined thicknesses between 2 mm and 20 mm are typical, however, thicknesses less than 2 mm or greater than 20 mm may also be suitable depending on the application and the size of the area to be scanned. The slice thickness setting control  40  may include a rotatable knob with discrete or continuous thickness settings. 
     The volume rendering processor  46  projects the rendering box  30  onto an image portion  48  of an image plane  34  (FIG.  2 ). Following processing in the volume rendering processor  46 , the pixel data in the image portion  48  may pass through a video processor  50  and then to a display  67 . 
     The rendering box  30  may be located at any position and oriented at any direction within the scanned volume  16 . In some situations, depending on the size of the region being scanned, it may be advantageous for the rendering box  30  to be only a small portion of the scanned volume  16 . 
     Once the rendering box  30  is placed over the scanned volume  16 , the volume rendering processor  46  performs a projection operation through the rendering box  30  to combine Voxels in adjacent image planes  34 . The adjacent Voxels are combined to form a single 2D rendered image. The Voxels to be combined are determined by the desired view and projection angle. For example, if a view is desired orthogonal to the rendering box  30 , the rendering process combines Voxels arranged along lines or rays extending perpendicular to, and through, the image planes  34 . 
     While the direction of projection onto the image portion  48  may be orthogonal to the center image plane  34 , it need not be orthogonal. For example, at relatively small scan angles  26 , the image planes  34  may not be parallel to one another, nor parallel to a reference coordinate system in which the image planes  34  are stored. Hence, if the rendering box  30  is parallel to the reference coordinate system, projection may occur at an angle to the image planes  34  and, in such a case, the direction of projection onto the image portion  48  is not orthogonal. Alternatively, the rendering box  30  may be defined at an angle to the reference coordinate system. 
     The scanned volume  16  may include a number of scan lines that have inconstant resolution. A reason for inconstant resolution is that when ultrasound echo beams are received, the echo beams vary in thickness along their length as a result of being out of focus at certain depths and in focus at other depths. The error of inconstant resolution may be reduced by a pre-defined constant thickness at the slice thickness setting control  40 . Increases in thickness generally reduce the error of inconstant resolution. The rendering box  30  need not have a pre-defined constant thickness. 
     The volume rendering processor  46  may perform several different filtering algorithms, such as averaging, median filtering, and the like between adjacent pixels in one image plane  34 . The volume rendering algorithms employed in connection with certain embodiments of the present invention increase the contrast of soft tissue (i.e., improve tissue differentiation). The amount of tissue differentiation depends on the selected pre-defined slice thickness, and on the object scanned. Typically, thicker slices result in higher contrast. 
     The volume rendering algorithms used in accordance with certain embodiments of the present invention to combine adjacent image planes  34  include the following general types: maximum intensity projection, minimum intensity projection, and surface rendering using fuzzy segmentation in combination with either the voxel texture information, the depth information, gradient shading and the like. Various particular rendering algorithms are described in detail in the book 3D Imaging in Medicine; Algorithms, Systems, Applications; Edited by Karl Heinz Hohne, Henry Fuchs, Stephen M. Pizer; NATO ASI Series; Springer Verlag 1990, which is hereby incorporated by reference. Combination of rendering algorithms can be applied in the volume rendering processor  46 . 
     The volume rendering algorithms may operate on relatively thin slices or thin rendering boxes  30  to improve the tissue contrast. When imaging some relatively small patient areas, taking a relatively thick rendering box  30  may cause a loss of information. For example, an operator may take a relatively thin rendering box  30  of a small tumor to avoid loss of information, whereas a relatively thick rendering box  30  may be taken of an organ such as a kidney to provide a significant improvement in contrast resolution of the large organ. Applying the volume rendering algorithms to relatively thin rendering box  30  results in an improvement of contrast of a B-image, particularly in small scanned volumes  16 . 
     In one embodiment, a real-time display of a region of interest results from a rendering mode that comprises a mixture of surface texture and transparent maximum rendering modes. The real-time display may give a physician more flexibility when diagnosing the region. In an alternative embodiment in which the rendering mode comprises a mixture of surface texture and transparent maximum rendering modes, the display is not real-time. Various ratios of surface texture and transparent maximum rendering modes may be employed on the rendering box  30 . For example, the final 2D image may comprise 60% of the gray value of the surface texture image plus 40% of the gray value of the transparent maximum image. Ratios other than 60% 1 40% are also suitable and include 80%/120%, 75%/25%, and 70%/30%. Other ratios may be applied. Surface texture and transparent maximum rendering modes result in less speckle pattern and a highly improved tissue contrast (i.e., the signal/noise ratio is improved). The improved tissue contrast facilitates the finding of diffuse lesions in organs. 
     Embodiments in which volume rendering algorithms are employed on relatively thin rendering boxes  30  to improve the tissue contrast can be used for the following 3D or 3D real-time (4D) acquisition modes or combinations of the following 3D or 3D real-time (4D) acquisition modes: conventional grayscale sonography, 2D compound imaging, tissue harmonic imaging, pulse inversion harmonic imaging, duplex sonography with color flow mapping (CFM), duplex sonography with power Doppler, or duplex sonography with spectral Doppler. 
     For the projection of a 3D rendering box  30  onto the display  67 , another embodiment of the present invention performs rendering in real-time 4D scanning, using a multi-planar display mode. A display  70  having multi-planar display mode is shown in FIG.  3 . For ease of description, all four images in the display  70  are shown schematically. Multi-planar display mode enables an operator to see the B-image that is being obtained  71  (in the upper left in FIG.  3 ), a plane  72  orthogonal to the B-image  71  and seen in the scan direction of the transducer movement, a coronal plane  74  which is orthogonal to the planes  71  and  72 , and an image  76  that has been volume rendered to enhance contrast. Real-time 4D scanning with multi-planar display is similar to the rendering of stored, static 3D volumes but is applied during 4D scanning. The projection of the rendering box  30  is made onto the coronal plane  74 . However, an operator can select to project the rendering box  30  onto any of the three planes  71 ,  72 , or  74 . A large volume sweep angle  26  may be chosen by an operator to switch the plane (e.g.,  71 ,  72 , or  74 ) onto which the rendering box  30  will be projected. Therefore there is a lower volume rate per second. For structures which do not move (such as a breast) the lower volume rate per second is not a problem. 
     For the projection of the 3D rendering box  30  onto the 2D display  67 , a further embodiment of the present invention performs volume rendering in real-time 4D scanning as a pseudo 2D mode. A very small volume sweep angle  26  is used. As seen in FIG. 4, a split screen  78  may be employed to show (a) a typical B-image on the plane  80  onto which volume rendering occurs and (b) an image  82  volume rendered in accordance with an embodiment of the present invention. Images  80  and  82  are shown schematically. Because of the small sweep angle  26 , there is a high volume rate (displayed images per second or frame rate). 
     In order to project the rendering box  30  onto the display  67 , some embodiments of the present invention perform rendering on stored, static 3D volumes. The process is similar to the process shown in FIG.  2  and discussed in connection with the real-time 4D volume rendering image embodiment shown in FIG.  2 . First an operator selects a desired plane to be the plane onto which projection occurs. Then the operator selects a suitable thickness. Following those two steps, the rendering box  30  has been created and can be moved freely within the stored volume. 
     While the invention has been described with reference to a preferred embodiment, it will be understood by those skilled in the art that various changes may be made and equivalents may be substituted without departing from the scope of the invention. In addition, many modifications may be made to adapt a particular situation or material to the teachings of the invention without departing from its scope. Therefore, it is intended that the invention not be limited to the particular embodiment disclosed, but that the invention will include all embodiments falling within the scope of the appended claims.