An approach for acquiring dimensionally accurate three-dimensional (3-D) ultrasound data from multiple 2-D image planes is presented. This is based on the use of a modified linear-phased array comprising a central imaging array that acquires multiple, essentially parallel, 2-D slices as the transducer is translated over the tissue of interest. Small, perpendicularly oriented, tracking arrays are integrally mounted on each end of the imaging transducer. As the transducer is translated in an elevational direction with respect to the central imaging array, the images obtained by the tracking arrays remain largely coplanar. The motion between successive tracking images is determined using a minimum sum of absolute difference (MSAD) image matching technique with subpixel matching resolution. An initial phantom scanning-based test of a prototype 8 MHz array indicates that linear dimensional accuracy of 4.6% (2 ) is achievable. This result compares favorably with those obtained using an assumed average velocity [31.5% (2 ) accuracy] and using an approach based on measuring image-to-image decorrelation [8.4% (2 ) accuracy]. The prototype array and imaging system were also tested in a clinical environment, and early results suggest that the approach has the potential to enable a low cost, rapid, screening method for detecting carotid artery stenosis. The average time for performing a screening test for carotid stenosis was reduced from an average of 45 minutes using 2-D duplex Doppler to 12 minutes using the new 3-D scanning approach.
An approach for acquiring dimensionally accurate 3D ultrasound data, based on a modified 1D transducer array, is presented. The method avoids many of the drawbacks of conventional approaches to 3D ultrasound data acquisition. Scanning is simple and easy to perform in a clinical setting.A modified 1D transducer array is employed comprising a central conventional 1D 'Imaging' array and two perpendicular 'Tracking' arrays -each integrally mounted at each end of the 'Imaging' array. As the transducer is scanned in the elevation direction of the central array, the images acquired by the 'Tracking' arrays remain coplanar and hence it is possible to accurately track image motion using any one of several image tracking techniques.Methods for improving the performance and ergonomics of the transducer array are presented. In particular, a crossed electrode transducer structure is proposed for minimizing the total transducer 'footprint' (contact surface area). The versatility of the approach in terms of its suitability for scanning breast, carotid and prostate is discussed. We have acquired both phantom and in-vivo 3D ultrasound data with the prototype imaging approach. Initial studies suggest that the linear dimensional accuracy in the elevation direction (i.e., the reconstructed direction) is approximately 5%. BACKGROUNDAlthough all anatomy is 3D dimensional in form, the vast majority of ultrasound imaging is 2D. Most of the time 2D provides sufficient information but there are clearly identifiable limitations: Volume MeasurementsWhile linear dimension and cross-sectional area can be determined from a 2D view, volume -arguably the most important clinical parameter -cannot be accurately determined. Current practice frequently calls for gross assumptions to be made regarding the relationship between the observed area and the estimated volume. This is frequently performed when estimating heart chamber volume using a limited number of 2D chamber cross-sectional views. Some views are impossible to obtainWhen using a 2D scanning probe it is not possible to obtain the 'C-Scan' view -i.e., a 2D slice parallel to the skin surface. Notice that an inability to obtain the 'perfect' 2D slice means that even an estimate of linear dimension or area may be erroneous. For example, if one is trying to measure the longest linear dimension of an organ of interest, then one must obtain a 2D view that includes the appropriate endpoints in 3D space. Optimal 2D scan views may be missedIt is common practice, particularly in the United States, for a non-M.D. trained sonographer to acquire one, or more, 2D image slices which are later 'read' by a fully qualified (i.e., M.D.) radiologist who makes the diagnosis. The radiologist is dependent on the sonographer's ability to obtain the most clinically significant view. If the radiologist is not satisfied with the view, then it may be necessary to recall the patient and make a second study. This results in significant inconvenience, delay and added, potentially unnecessary, cost. A better clinical pract...
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