Ultrasonic diagnostic apparatus capable of acquiring high quality image by correcting phase distortion contained in ultrasonic pulses

Abstract: In an ultrasonic diagnostic apparatus (1000), ultrasonic propagation time differences contained in echo signals reflected from a biological body under medical examination are corrected by comprising: a quadrature phase detecting unit (30:130:25) for quadrature-phase-detecting the echo signals derived from an ultrasonic transducer probe (2) to obtain as phase data a quadrature signal component and an in-phase signal component; a delay-time correcting value calculating unit (23) for calculating at least one of delay-time correcting values used for the energizing signals and the echo signals based upon both of the quadrature signal component and in-phase signal component; and, a delay controlling unit (13) for controlling at least one of delay time data previously given to the energizing signals and echo signals based upon one of calculated delay-time correcting values.

Description: The present invention generally relates to an ultrasonic diagnostic apparatus according to the pre-characterizing part of claim 1. Such apparatus is used to acquiring ultrasonic images of a biological body. More specifically, the present invention is directed to an ultrasonic diagnostic apparatus capable of improving image qualities of the acquired ultrasonic images with respect to unequal portions within the biological body based upon fluctuations in arrival times of the echo signals. In an ultrasonic diagnostic apparatus as disclosed in DE-A-37 42 724, the echo signals derived from a plurality of transducer elements arranged in an array form, are detected by a guadrature-phase detecting means so as to obtain quadrature and in-phase signal components as phase data against a reference signal. Data on delay times which are determined based on geometrical positional information with respect to the respective transducer elements, are electrically given to the echo signals reflected from interiors of a biological body. Energizing signals are used to transmit ultrasonic pulses from the transducer elements toward the biological body. Based upon the delay time data, a focal point of the echo signals is defined by the known in-phase additional process so as to obtain a desirable ultrasonic image of the biological body. The focal point is scanned under electronic scanning control, for instance, in a plane form. More specifically, while several tens to several hundreds of rasters are transmitted/received, a "B-mode" ultrasonic image is obtained in an image constructive unit. The above-described known ultrasonic imaging technique will now be described more in detail with reference to Figs. 1 to 3. As shown in Fig. 1, under such conditions that the velocity of sound which passes through a propagation medium I o from a transducer element "V" to a focal point is uniform, and this sound velocity is known, when the respective transducer elements are energized by receiving data on delay times "d 1 " to "d n " ("n" being an integer greater than 2) which has been defined based on the focal point "C" and the geometric positional data, a focal point "C" at which ultrasonic pulses are fully focused can be formed without serious phase shifts. However, in case that organs within a biological body "P" are to be ultrasonic-imaged, as represented in Fig. 2, the ultrasonic pulses transmitted from the transducer elements "V" are propagated through a surface layer "P f " of thebiological body "P", which is constructed of fat and muscle made of unequal propagation mediums I and II. If the delay times "d 1 " to "d n " are given to process the energizing signals for the transducer elements "V" in a similar method as in Fig. 1, there are phase shifts in the ultrasonic pulses near another focal point C'. As a result, this focal point C' is widened, as compared with the first-mentioned focal point C, and also both special resolution and contrast resolution of the resultant ultrasonic image are lowered. Also to form such a sufficiently focused point "C", even when the organs having the unequal propagation mediums I and II are ultrasonic-imaged without any phase shift, it has been proposed that the delay correction values which have been obtained by way of the conventional correlation method, are added to the delay times determined by the geometric positional information on the respective transducer elements and this focal point C. Thus, the image characteristics of the ultrasonic images are improved. This conventional correlation method is described in, for example, Japanese Patent Disclosure No. 53-51846 (1988); see also EP-A-0 256 481 which discloses the features mentioned in the pre-characterizing part of claim 1. In accordance with one of the conventional correlation, as illustrated in Fig. 3, after the correlation function "F" has been calculated with respect to one pair of echo signals received by two certain transducer elements (see Fig. 2), time "t p " indicative of a peak value "F p " in this correlation function "F" is found out; a time difference "Δt" between this time "t p " and a predetermined reference time "to" is calculated; and then the delay times produced in the echo signals received by two certain transducer elements are corrected based on this time difference information "Δt". However, since the above-described conventional correlation method requires an extremely large computation scale, there are problems that this correlation method is not suitable for improving the realtime image processing and impedes a compactness of the ultrasonic diagnostic apparatus. In the following, another delay correction method with respect to plural focal points is considered. As shown in Fig. 4, when ultrasonic pulse beams are focused onto two focal points "O" and "Q" of the biological body "P" which are positioned along a depth direction of this body by employing an ultrasonic probe "P b " having "M" pieces of transducer elements, the propagation paths of these ultrasonic pulse beams are different from each other. In such a case, delay correction values different from each other are required with respect to two focal points "O" and "Q" by measuring the phase differences (i.e., time difference in propagation) of the echo signals. In actual, not only two focal points "O", "Q", but also many other focal points are present within the biological body "P". Assuming now that a total number of ultrasonic scanning beams is "i" and a total number of focal points along each of the ultrasonic scanning beams is "j", a total focal point of this biological body "P" to be imaged amounts to i × j. Normally, "i" = 100 to 300 and "j" = 10 to 30. Accordingly, the entire focal points amount to 1000 to 9000. There is a second problem that a large quantity of delay correction values must be calculated based on the conventional correlation method, which is not practically possible. Furthermore, there are non-reflection (non-echo) portions within a biological body such as cholecystics and blood vessels, from which ultrasonic beams are not reflected as the echo pulses. If a focal point to be ultrasonic-imaged is selected at cholecystics, no reflection signal (echo signal) is obtained therefrom, so that no delay correction value of this focused cholecystics portion is calculated. Accordingly, there is a third problem that reflection signals suitable for ultrasonic measurements are not always obtained. The object of the present invention is to provide such an ultrasonic diagnostic apparatus capable of improving ultrasonic image quality in a real time, wherein the apparatus is capable of forming a focal point within a biological body without any phase shift. This object is achieved by the features of claim 1. The present invention provides an ultrasonic diagnostic apparatus capable of correctly evaluating echo signals reflected from various biological conditions of a biological body. The apparatus is capable of precisely correcting delay amounts of transmitting/received signals, namely, fluctuation contained in signal propagation time. For a better understanding of these and other objects of the present invention, reference is made of the following detailed description of the invention to be read in conjunction with the following drawings, in which: Figs. 1 to 4 are illustrations for explaining widened focal points of the conventional ultrasonic diagnostic apparatus; Fig. 5 is a schematic block diagram for showing an arrangement of an ultrasonic diagnostic apparatus 1000 according to a first embodiment of the present invention; Figs. 6 to 8 illustrate operations of the first ultrasonic diagnostic apparatus 1000; Fig. 9 is a schematic block diagram for showing an arrangement of an ultrasonic diagnostic apparatus 2000 according to a second embodiment of the present invention; Figs. 10 to 15 illustrate operations of the second ultrasonic diagnostic apparatus 2000; Fig. 16 is a schematic block diagram for showing internal diagrams of the discontinuity correcting section 121A and a temporal direction averaging section 121B represented in Fig. 9; and Fig. 17.is a schematic block diagram for representing an arrangement of an ultrasonic diagnostic apparatus 3000 according to a third embodiment of the present invention. Before describing various types of preferred embodiments,.a first basic idea of an ultrasonic diagnostic apparatus according to the present invention will now be summarized. When a phase detecting means processes reception signals (i.e., echo signals) received by a plurality of transducer elements so as to detect phases of the respective echo signals, a converting means will convert these phase data into corresponding delay time data. Then, a correcting means corrects a predetermined delay time based on the converted delay time data, whereby since the corrected delay times corresponding to propagation mediums of a biological body under medical examination are electronically applied to both the energizing signals and echo (reflection) signals for the plural transducer elements, a focal point can be formed with a slight phase shift. In case that the phase data outputted from the phase detecting means contains discontinuities along the array direction of the transducer elements, a phase correcting means corrects these phase discontinuities to obtain phase continuities. As a result, the correct phase data having no error caused by these discontinuities may be inputted into the converting means. Furthermore, a control means controls data write/read-operations to a plurality of memories, and also controls such that the delay time data obtained by way of the predetermined calculating process are applied to both the energizing signals and echo signals so as to newly acquire ultrasonic images of the biological body, whereby a focal point with a less phase shift can be formed in a real time. ARRANGEMENT OF FIRST ULTRASONIC DIAGNOSTIC APPARATUS I. OVERALL ARRANGEMENT In Fig. 5, there is shown an ultrasonic diagnostic apparatus 1000 according to a first preferred embodiment of the present invention, that is realized by utilizing the above-described first basic idea of the present invention. The first ultrasonic diagnostic apparatus 1000 mainly comprises an ultrasonic probe 2 having a plurality of transducer elements V arranged in an array form (as shown in Fig. 1); a multiplexer 3 for sequentially energizing the plural transducer elements V; a display system 10 for displaying an ultrasonic image of a biological body under medical examination (not shown in detail) in response to echo signals derived from the transducer elements V; and a signal correction system 20 for correcting delay times of energizing signals and echo (reception) signals of the transducer elements. More specifically, the display unit 10 includes an energizing signal generating section 11 for producing the energizing signals having a predetermined central frequency, e.g., 3MHz with a narrow bandwidth, and also a reference signal "S 1 " to be supplied to the signal correction system 10; a reception delay circuit 12 for applying a predetermined delay time to the echo signals; an adder 15 for performing an addition process with respect to these signals; and a delay control section 13 having a delay time memory (not shown in detail), for applying delay times to the above-described energizing signal generating circuit 11 and reception delay circuit 12; and furthermore a display section 14 equipped with a television monitor (not shown in detail) for displaying ultrasonic images of the biological body thereon. Into the delay time memory employed in this delay control section 13, predetermined delay time data produced based on geometric positional information about the tansducer elements V are stored, which are supplied to the signal correction system 20 in order that the corrected delay times are produced and used in the energizing-signal generating section 11 and reception delay circuit 12. It should be noted that a total number of these transducer elements V is selected to be "m" ("m" being an integer greater than 2) in this preferred embodiment, and therefore "m" pieces of echo signals are received by the transducer elements V. The signal correction system 20 includes a phase detecting section 30 for detecting phases of the received echo signals by processing the echo signals received from the probe 2 via the multiplexer 3; a phase correcting section 21 for correcting discontinuities contained in the phase data detected by the phase detecting unit 30; a storage unit 22 for storing therein continuous phase data which are obtained from the phase correcting unit 21; and a converting section 23 for performing one process to convert the data and the other process to interpolate the data. The signal correction system 20 further includes a central processing unit 24 which may function as a correction means for correcting the delay time data stored in the delay time memory of the delay control section 13 based on the delay time data converted by the converting section 23; and a 90°-phase shifter 25. The phase detecting sections 30-1 and 30-2 are employed so as to detect phase information as ultrasonic Doppler information, which is well known in the art. One phase detecting section 30-1 is constructed of a first mixer 32A, a second mixer 32B, a first low-pass filter 35A, a second low-pass filter 35B, a first integrator 35A, a second integrator 35B, and an arc tangent (tan -1 ) circuit 36. The first mixer 32A mixes a signal "S" derived from the reception delay circuit 12 with a reference signal "(cos ωt) S 1 " that is synchronized with the energizing signal outputted from the energizing signal generating section 11. The second mixer 32A mixes the above-described signal "S" derived from the reception delay circuit 12 with a signal (sin ωt) S 2 which is produced by phase-shifting the reference signal S 1 from the energizing signal generating section 11 in the 90°-phase shifter 25 by 90°. These signal phase correcting sections 30-1 and 30-2 perform the above-described signal process by inputting therein the reception signals "S" with respect to all rasters or every several rasters. It should be noted that the angular frequency "ω" of two reference signals (cos ωt) S 1 and (sin ωt) S 2 supplied from the energizing signal generating section 11 to the first and second mixers 32A and 32B, are selected to be one of frequencies of the reception (echo) signal "S". The function of the first and second integrators 35A and 35B is to integrate the echo signals, thereby obtaining an averaged phase within a certain range of the reception signals. II. SIGNAL CORRECTING SYSTEM With respect to the respective arrangements in the signal correcting system 20, the following description will be made of such an example where a reception (echo) signal "S k (t)" is received by a k-th transducer element of the probe 2 ("k" being an integer smaller than "m"). Assuming now that an amplitude of this echo signal S k (t) is A k (t) and a phase thereof is  k , the reception signal S k (t) received by the k-th transducer element (not shown in detail) is expressed by: S k ·(t) = A k (t) cos ( ωt +  k ) This echo signal S k (t) is mixed with the above-described reference signals S 1 and S 2 in the first and second mixers 32A and 32B, respectively. When the mixed signal is expressed as a complex signal Z k (t), it is given: Z k (t) = A k (t) • [ cos (2ωt+ k ) + cos ( k ) ] + j { A k (t) • [ sin ( k ) - sin (2ωt+ k )]} Furthermore, when this complex signal Z k (t) is filtered in the respective low pass filters 34A and 34B in order to remove a high frequency signal component of "2ω" by the first or second low pass filters 34A or 34B, another complex signal Z k (t) is outputted from the relevant low-pass filter 34A, 34B, which is expressed by the following equation (3): Z k (t) = A k (t) cos ( k ) + j { Ak(t) sin ( k )} Thereafter, this complex signal Z k (t) outputted from the low-pass filter 34A or 34B is calculated in the arc tangent circuit 36 in accordance with the following equation (4), whereby phase data " k " is obtained therefrom and is supplied to the phase correcting section 21:  k = tan - {[ A k (t) sin ( k )] / [ A k (t) cos ( k )]} = tan - {[ sin ( k ) / cos ( k )} = tan - {[ tan ( k ) } As previously explained, "n" pieces of phase data ( 1 to  n ) are inputted into the phase correcting section 21 within a phase range from "-π" to "+π", as shown in Fig. 6. The function of this phase correcting section 21 is to couple discontinuities f (f 1 , f 2 ) with each other contained in the phase distribution data under control of CPU 24. As shown in Fig. 6, these discontinuities f (f 1 , f 2 ) are coupled with each other and then are obtained as the continuous phase distribution data as shown in Fig. 7. The continuous phase distribution data are supplied to the respective storage sections 22 (22a to 22c) every image constructive unit (data constituting one image), in the following referred to as image unit. III. STORAGE & CONVERTING SECTIONS As represented in Fig. 5, the storage section 22 employs three RAMs 22a to 22c. Under control of CPU 24, changing switches "A", "B" and "C" are operated every one image unit in order that both the phase data from the phase correcting section 21, and the delay time data which has been converted and interpolated by the converting section 23 are sequentially written into these RAMs 22a to 22c. The function of the converting unit 23 is to convert the phase data obtained every all rasters, or several rasters into delay time data, and also to interpolate the delay time data with respect to the skipped (or not processed) several rasters while acquiring the phase data every several rasters. Under control of CPU 24, the predetermined delay time data stored in the delay time memory of the delay time control unit 13, is corrected every one image unit based on the converted/interpolated delay time data. OVERALL OPERATION OF FIRST ULTRASONIC DIAGNOSTIC APPARATUS An overall operation of the first ultrasonic diagnostic apparatus 1000 will now be described with reference to the above-described Figs. 5 to 7 together with Fig. 8 showing contents of the data process and memories. Upon commencement of ultrasonic imaging operation by attaching the ultrasonic probe 2 to a surface of the biological body, an ultrasonic image of the biological body is acquired by the first ultrasonic diagnostic apparatus 1000, for instance, in a B-mode under control of CPU 24. The delay control section 13 delay-controls the energizing signal generating section 11 and adder 15 based on the predetermined delay time data stored in the delay time memory employed therein. The probe 2 performs B-mode scanning operation with respect to first image unit under control of CPU 24. Accordingly, a B-mode ultrasonic image of the first image unit is displayed on the TV monitor of the display section 14 employed in the display system 10. It should be noted that at this stage, since the predetermined delay time data have not yet been corrected in accordance with the propagation mediums within the biological body, the sufficiently focused focal point is formed, resulting in lowered space resolution. Subsequently, B-mode images are successively displayed on the TV monitor of the display section 14 after second and subsequent image units. According to the feature of this first ultrasonic diagnostic apparatus 1000, when the B-mode image data on the first image unit is acquired, the signal correction system 20 calculates delay times for correction purposes in response to the reception signal "S" from the multiplexer 3 and therefore corrects the predetermined delay time data which have been stored in the delay time memory of the delay control section 13 based on the calculated correcting delay times, thereby to obtain desirable delay times corrected by taking account of the propagation mediums constructing the biological body. SIGNAL CORRECTION The process of the signal correcting system 20 will now be described more in detail. Fig. 8 represents contents of the signal process operations and of the memory RAMs 22a to 22c with respect to the image unit. In Fig. 8, symbol "W" indicates write operation of data into RAMs 22a to 22c; symbol "R" denotes read operation of data from RAMs 22a to 22c; reference numerals written with these symbols "W" and "R" indicate numbers of the image unit; and symbols "A", "B", "C" represent switching operations of the switches A to C (see Fig. 5). During the B-mode scanning operation for the first image unit, the received (echo) signals are phase-detected by the phase detective section 30 and then the discontinuities (f 1 , f 2 ) contained in the phase-detected echo signals are corrected by the phase correcting section 21 based upon the phase detected information, and the resultant image data are represented as "W-1-A". The image data "W-1-A" are written into RAM 22a while the switch "A" is actuated. Next, while the B-mode scanning operation is performed for the second image unit by energizing the probe 2, the converting section 23 receives the phase-corrected data "R/W-1-B" which have been previously written into the RAM 22a and acquired based on the phase-corrected data on the first image constructive unit. Then, the phase-detected data "R/W-1-B" are converted into the desirable delay time data by this converting section 23, which are written into the RAM 22a. On the other hand, the phase-corrected data on the second image unit are represented as "W-2-A", which are derived from the phase correcting section 21, and written into RAM 22b by operating the switch "A". Subsequently, while the B-mode scanning operation for the third image unit is carried out by energizing the probe 2, the delay control section 13 reads out the delay time data on the first image unit stored in RAM 22a, as indicated by "R-1-C", and performs the correction when the transmission/reception delay operations are actually performed. Thereafter, the phase-corrected data on the second image unit stored into RAM 22b, as indicated as "R/W-2-B", are acquired and converted into the corresponding delay time data in the converting section 23. Also, these phase-corrected data are written into RAM 22b, and the phase-corrected data denoted by "W-3-A" are written from the phase correcting section 21 into RAM 22c by operating the switch "A". Then, the desirable focal point with the less phase shift can be formed based upon this B-mode image scanning operation and therefore the B-mode images can be formed with the improved spatial resolution and contrast resolution on the display section 14. Subsequently, the image data on the third and subsequent image units are similarly processed and the resultant processed image data are written/read from RAM 22a to 22c. In accordance with the first ultrasonic diagnostic apparatus 1000, after the third image unit, since the delay time data acquired under real time characteristics delayed for three image units and corrected by taking account of the propagation medium of the biological body are electronically applied to both the energizing signals and echo signals of the transducer elements, the focal point with the small phase shift can be formed and the ultrasonic images with the better image quality can be obtained. OVERALL ARRANGEMENT OF SECOND ULTRASONIC DIAGNOSTIC APPARATUS Fig. 9 is a schematic block diagram of an ultrasonic diagnostic apparatus 2000 according to a second preferred embodiment of the present invention. It should be noted that the same reference numerals shown in Fig. 5 will be employed as those for denoting the same circuit elements shown in the following figures. Also, this second ultrasonic diagnostic apparatus 2000 is realized based on the first basic idea of the present invention. As apparent from Fig. 9, a major different construction of the second ultrasonic diagnostic apparatus 2000 from the first ultrasonic diagnostic apparatus 1000 is to newly employ a phase detecting section 130 and a phase correcting section 121 of a signal correcting system 120. The phase detecting section 130 corresponds to the phase detecting section 30 of the first ultrasonic diagnostic apparatus 1000 from which the first and second integrators 35A and 35B are omitted. Since the integrators 35A and 35B are omitted from this phase detecting section 130, the function of this phase detecting section 130 is to obtain instantaneous phase data at time instants "t 1 " to "t n " as shown in Fig. 10. This drawing indicates a discontinuity "f" occurring at the respective time instants "t 1 " to "T n " along the array direction of the transducer elements V. The above-described phase correcting section 121 is arranged by a discontinuity correction section 121A and a temporal direction averaging section 121B. The discontinuity correction section 121A corrects the discontinuities of the phase data (see Fig. 11) every time instants "t 1 " to "t n ". The temporal direction averaging section 121B averages the phase data at the respective time instants "t 1 " to "t n " the discontinuities of which have been corrected, and obtains such a phase distortion pattern as shown in Fig. 12. DISCONTINUITY CORRECTING OPERATION The above-described discontinuity operation by the discontinuity correcting section 121A will now be described more in detail with reference to Figs. 13 to 16. The major operation of this discontinuity correcting section 121A is such that after the discontinuity point "f" has been searched, a bias value is applied to the phase data at this discontinuity point "f" so as to obtain continuous phase data without any discontinuities. In a concrete example, first, a starting point "f 10 " of the calculating process for the equation (5) is selected. It should be understood that although an end point at the left side of Fig. 13 is selected to be "f 10 ", any other points may be selected to be this end point. Also, it should be noted that a bias value at this starting point "f 10 " is selected to be "O". The phase difference calculation is carried out is such a manner that a phase difference "Δ" is first calculated between the starting point "f 10 " and the adjacent point "f 10-2 ", and subsequently, another phase difference Δ is calculated between this point "f 10-2 " and the adjacent point "f 10-3 ". The calculation results are represented in Fig. 14. As apparent from Fig. 14, for instance, at the discontinuity points f 11 and f 12 , the following calculation result (6) is given:  3 -  2 ≒ - π - ( + π ) ≒ - 2 π Thus, as to the discontinuity points f 11 and f 12 ; f 15 and f 16 ; f 23 and f 24 , which suddenly change from a positive to a negative, the calculation results become discontinuity points f 13 and f 14 ; f 17 and f 18 ; f 19 and f 20 ; f 21 and f 22 , which suddenly change from a negative to a positive, the calculation results become +2π approximately. Then, to determine bias values, a comparison is made between the calculation results shown in Fig. 15 and a threshold level "α". That is, based on the following inequality (7), assuming now that the threshold level "α" is selected to be 1.9π, a bias value of ± 2π is given to the phase difference Δ ≧ 1.9π; a bias value of + 2π is given to the phase difference Δ < 0 (namely "negative") and a bias value of - 2π is given to the phase difference Δ > 0 (namely "positive"). It should be noted that this comparison is performed under such a condition that the phase difference Δ between the adjusting signals is smaller than the threshold level "α" except for the discontinuity point "f", and also the values denoted in the parenthesis of Fig. 14 represent the finally given bias values with respect to the starting point "f 10 ". When such bias values are given to the phase data shown in Fig. 13, the continuous phase data where no discontinuity point "f" is present at a certain time instant can be obtained as represented in Fig. 15. Fig. 16 is a schematic block diagram for showing an internal arrangement of the discontinuity correcting section 121A and temporal direction averaging section 121B. In the discontinuity correcting section 121A, the phase data are supplied from the phase detecting sections 130-1 and 130-2 and stored in corresponding memories 122-1 through 122-n. These phase data stored in the memories 122-1 to 122-n are selectively and successively read and supplied to both a subtracter 124 and a bias applying circuit 125 by operating a switch 123. The subtracter 124 successively subtracts the phase data on the adjacent echo signals from each other to obtain the phase differences Δ. The resultant phase differences Δ are supplied to a bias judging circuit 126. The bias judging circuit 126 judges the phase data based upon the phase difference data Δ and the threshold value "α" so as to determine a proper bias value. As a result of this judgement, the bias applying circuit 125 applies the proper bias value such as +2π to the phase data, whereby the discontinuity point contained in this phase data can be corrected, resulting in the continuous phase data. Then, the continuous phase data are successively obtained from the discontinuity correcting section 121A and thereafter furnished to a first memory 127A of the temporal direction averaging section 121B. A plurality of continuous phase data are averaged in an averaging circuit 128 thereby to obtain the final continuous phase data from which the discontinuities have been eliminated (see Fig. 15). With the above-described arrangements, especially the discontinuity correcting section 121A and temporal direction averaging section 121B, the second ultrasonic diagnostic apparatus 2000 has such a particular advantage that even when the phase data outputted from the phase detecting section 130 contains the discontinuities "f", the discontinuities can be surely corrected by the phase correcting section 121, in addition to the previous advantages of the first ultrasonic diagnostic apparatus 1000. As a consequence, there is less calculation error caused by the discontinuities contained in the phase data. Since the focal point of the ultrasonic pulses can be formed without any phase shifts contained therein, the ultrasonic images of the biological body with the better image quality can be stably obtained. ARRANGEMENT OF THIRD ULTRASONIC DIAGNOSTIC APPARATUS Referring now to Fig. 17, an ultrasonic diagnostic apparatus 3000 according to a third preferred embodiment of the present invention, which is accomplished based on the first basic idea, will be described. As apparent from Figs. 5 and 17, the third ultrasonic diagnostic apparatus 3000 employs only a different circuit element, as compared with the first ultrasonic diagnostic apparatus 1000. That is, a second multiplexer 221 and a converting section 223 are newly employed. The second multiplexer 221 successively transfers the phase data  1 to  n outputted from the phase detecting sections 30-1 and 30-2, via the switch to the storage section 22 under control of CPU 24. The converting section 225 owns the similar function to the phase correcting section 121 of the second ultrasonic diagnostic apparatus 2000 shown in Fig. 9. That is, this converting section 223 performs such a phase correcting process similar to that of the phase correcting section 121; such a converting process that the phase data acquired for all rasters or every several rasters are converted into delay time data; and also such a delay time data interpolation that the data interpolation is performed for the delay time data on the skipped several rasters while the phase data are acquired every several rasters. With the above-described arrangements, the third ultrasonic diagnostic apparatus 3000 has the similar effects and advantages as those of the second ultrasonic diagnostic apparatus 2000.

Claims: An ultrasonic diagnostic apparatus (2000) comprising: ultrasonic transducer means (2) having a plurality of ultrasonic transducer elements (V) for transmitting ultrasonic pulses to an object under medical examination in response to energizing signals, and for receiving echoes therefrom to produce echo signals (S), delay controlling means (11, 12, 13) supporting the energizing signals and the echo signals (S) with delay times determined according to the geometrical position information of the transducers elements, delay-time-correcting-value-calculating means (23) calculating delay-time correcting values, and delay-time-correcting means (24) correcting the delay time in said delay control means (13) by the delay-time correcting values to form a focal point without phase shifts, which is characterized by: quadrature-phases-detecting means (25, 130) for inputting the echo signals derived from the transducer means (2) and reference signals (S1, S2), and for obtaining phase data () based on a quadrature signal component and an in-phase signal component contained in the echo signals, discontinuity correcting means (121A) for correcting the phase data in such a manner that discontinuity points (f1, f2, ..., fn) contained in the phase data are searched and, in response to identified discontinuity points, the corresponding discontinuities in the phase data are removed by adding bias values in the form ±2π so as to provide continuous phase data, temporal direction-averaging means (121B) for averaging the continuous phase data, and said delay-time-correcting-value-calculating means (23) calculating the delay-time correcting values based on the averaged continuous phase data. An ultrasonic diagnostic apparatus (2000) as claimed in claim 1, wherein said delay-time-correcting-value calculating means (23) further performs an interpolation process based on the actually received echo signals while only a predetermined number of transducer elements (V; 43) are energized by the energizing signals, whereby the echo signals with respect to all transducer elements are obtained. An ultrasonic diagnostic apparatus (2000) as claimed in claim 1 or 2, wherein said discontinuity correcting means (121A) and said temporal direction-averaging means (121B) are interposed between the quadrature-phases-detecting means (25, 130) and the delay-time-correcting-value-calculating means (23). An ultrasonic diagnostic apparatus (2000) as claimed in claim 1 or 2, wherein said discontinuity-correcting unit (121A) calculates a phase difference (Δ) between the echo signals derived from adjacent transducer elements so as to search discontinuity points (f1, f2, ... fn) contained in the phase data. An ultrasonic diagnostic apparatus (2000) as claimed in claim 1 or 2, wherein said quadrature-phases-detecting means (25, 130) includes: mixing means (32A, 32B) for mixing the echo signals (S) with a first reference signal (S1) and mixing the echo signals (S) with a second reference signal (S2) which is phase-shifted from the first reference signal (S1); filtering means (34A, 34B) for filtering the echo signals mixed with the reference signals (S1, S2) so as to remove a high frequency signal component; and arc tangent means (36) for obtaining the phase data () from the echo signals filtered by the filtering means (34A, 34B).

Inventors: KANDA RYOICHI, SUMINO YOICHI, KANDA, RYOICHI, SUMINO, YOICHI
Applicants: TOSHIBA KK, KABUSHIKI KAISHA TOSHIBA
Application year: 1991
Main classification: A61B8
IPC codes: A61B8, G01S7