Ultrasonic probe having backing material layer of uneven thickness

Abstract: An ultrasonic probe (200) includes a piezoelecric material layer (10, 10a, 10c) having a pair of electrodes (11, 11a, 11c, 12, 12a, 12c) provided on both main surfaces thereof for applying voltage thereto, and a backing material (30) provided on one electrode (11, 11a, 11c). The backing material (30) has an acoustic impedance lower than that of the piezoelectric material layer (10, 10a, 10c). Interposed between the backing material (30) and one electrode (11, 11a, 11c) is an acoustic reflecting material layer (50, 50a, 50b, 50c) which has a thick first portion and a thin second portion. The second portion may have a substantially zero thickness to allow the backing material (30) to be in partial contact with one electrode (11, 11a, 11c). Thereby, the ultrasonic probe (200) can transmit and receive ultrasonic waves at its resonance frequencies. Also provided is an ultrasonic diagnostic apparatus (FIGS. 15 and 16) which displays an image resultant from combining images having the frequencies obtained by driving the ultrasonic probe (200).

Description: BACKGROUND OF THE INVENTION Field of the Invention The present invention relates to an ultrasonic diagnostic apparatus. Description of the Prior Art Ultrasonic diagnoses have been extensively popularized as image diagnostics of high simplicity. safetiness. and economy and have been spreading the range of the examining subject in almost all the realm of the living body. Especially in the examination of the living body. however, different frequencies must be used depending on subjects to be examined. In the prior art. since the available frequencies are specific to respective ultrasonic probes, multiple kinds of ultrasonic probes are generally required for respective subjects. In the examination of the living body. for example, probes having a high frequency, e.g. 5 - 10 MHz. for examining the shallow regions and ones having a low frequency, e.g. 3.5 - 5 MHz. for examining the deeper regions. As stated above. it has been an inconvenience that probes having different frequencies have to be selected for use depending on subjects to be examined. Consequently, a broad-banded ultrasonic device using a single probe capable of transmitting and receiving various frequencies from low frequencies to high frequencies is now strongly called for. Up to the present. several types of ultrasonic probes capable of transmitting and receiving a plurality of frequencies have been invented. For example, there are a type laminated with piezoelectric transducers each having different resonant frequency as taught in the Japanese patent laid-open publication Nos. 73861/1983, 172600/1988, and 173954/1988, a type devised with acoustic matching layers as disclosed in the Japanese patent laid-open publication No. 255044/1988, and a type comprising piezoelectric transducers having different resonant frequencies and alternately arranged as shown and described in the Japanese patent laid-open publication No. 68000/1987. Any of those types has a defect, such as a complicated structure causing difficulties in manufacture or a narrow band for frequency response. The laminated type of ultrasonic probe, for example, requires to have a structure laminated with as many piezoelectric transducers as the number of different frequencies, causing complexity in manufacture and less economy. Also, with respect to the characteristics, since the laminated type has a structure with piezoelectric transducers having different resonant frequency laminated toward the direction of ultrasonic waves transmitted and received by the probe, the piezoelectric transducers act upon each other to interfere with the ultrasonic wave propagation when the probe transmits and receives ultrasonic waves, resulting in difficulty of obtaining acceptable results. Further, in the type devised with acoustic matching layers, as the band cannot be widened more than that of the piezoelectric transducer, it is difficult to obtain satisfactory characteristics. Still further, the type with alternately arrayed piezoelectric transducers having different resonant frequencies can be used in the form of an array type of ultrasonic probe. though the density in array of transducers having the same frequencies is low. Therefore. it is difficult to satisfy the most important requirements. for the array type probe. that the array density of transducers be high and an ultrasonic sound field capable of transmitting and receiving ultrasonic waves having high directivity with the grating lobe suppressed as much as possible be formed. resulting in degradation of the characteristics. In addition. as a type different from those described above, in the Japanese patent laid-open publication No. 22040/1983 there is proposed an array type of probe in which arranged are the piezoelectric transducers which are continuously different in thickness in the direction perpendicular to the scanning direction to cause the resonant frequencies to continuously differ from each other in that direction. This system. however. also has a great difficulty in manufacture of the above-mentioned piezoelectric transducers and is hard to be put to practical use. Another type of electro-acoustic transducer element and an arrangement used for measurement of the non-tuning conversion loss including such transducer is disclosed in EP-A-0 015 886. In this known transducer element there is used a polymer piezoelectric film and an additional layer of like acoustic impedance coupled to the front or rear side of the piezoelectric film. Adjustment of the overall thickness of the additional layer enables variation in the frequency characteristics of the transducer element. An ultrasonic testing head comprising a damper, a protector and an ultrasonic wide-band axisymmetric varying thickness transducer disposed inbetween is disclosed in GB-A-1505411. The transducer in this testing head either has a planar end face connected to the damper and a profiled end face covered by the protector having a complementary profiled end face and a planar outer end face or both end faces of the transducer are profiled with complementary opposed end faces of the damper and the protector. This design stabilizes the amplitude of emitted and received ultrasonic oscillations by reducing influence of variations in the thickness of a coupling liquid between the testing head and an object being checked upon the frequency characteristic of the transducer. SUMMARY OF THE INVENTION It is the object of the present invention to provide an ultrasonic diagnostic apparatus comprising an ultrasonic probe having comparatively little difficulties in manufacture and a broad frequency bandwidth. In accordance with the present invention there is provided an ultrasonic diagnostic apparatus comprising: transmission means for generating a frequency voltage having a plurality of frequencies and for feeding the frequency voltage to an ultrasonic probe; said ultrasonic probe being provided for generating ultrasonic waves in response to the frequency voltage and electric signals in response to received ultrasonic waves; said ultrasonic probe comprising: a layer of piezoelectric material having generally flat main surfaces; a pair of electrodes provided on the flat main surfaces of said layer of piezoelectric material to apply the frequency voltage to said layer of piezoelectric material; a layer of backing material provided on one of said pair of electrodes and having an acoustic impedance lower than that of said layer of piezoelectric material; and a layer of reflecting material interposed between said one electrode and said layer of backing material and having an acoustic impedance higher than that of said layer of piezoelectric material; said layer of reflecting material including a first portion forming a center portion and a second portion forming a peripheral portion of said first portion so as to transmit wideband ultrasonic waves in a range of λ/2 to λ/4 resonant modes, said first portion having a thickness thinner than that of said second portion including a zero thickness; receiver means for receiving the electric signals from said ultrasonic probe; image visualizing means for producing images represented by the electric signals received by said receiver means; said image visualizing means comprising: image combining means for combining the images represented by the electric signals; and image display means for visualizing the combined images. In the ultrasonic probe apparatus in accordance with the present invention. a layer of backing material includes a first portion having an acoustic impedance lower than that of a layer of piezoelectric material and a second portion having an acoustic impedance higher than that of the layer of piezoelectric material. both portions of which are arranged on the back surface of the layer of piezoelectric material. Thus. a λ/2 resonance on the first portion and a λ/4 resonance on the second portion give rise to the total resonances having different frequencies obtained. Consequently. use of the ultrasonic probe in the ultrasonic diagnostic apparatus makes it possible to obtain by a single kind of ultrasonic probe not only two tomographic images of a subject with diffenrent frequencies but also a composite tomographic image resultant from the two tomographic images. In the ultrasonic probe used in the ultrasonic diagnostic apparatus in accordance with the present invention. the layer of backing material also has an acoustic impedance higher than that of the layer of piezoelectric material and is formed. for example. into a shape with thickness gradually decreasing toward the center of the layer of piezoelectric material. Thereby, the ultrasonic probe apparatus can realize a broad-banded operation capable of continuously covering resonant frequencies from the λ/2 resonance mode up to the λ/4 resonance mode. As a result. in all the depths of an subject and an ultrasonic tomographic image with a high S/N ratio can be obtained. BRIEF DESCRIPTION OF THE DRAWINGS The objects and features of the present invention will become more apparent from the consideration of the following detailed description taken in conjunction with the accompanying drawings in which: FIG. 1A is a sectional view showing an illustrative embodiment of an ultrasonic probe in accordance with the present invention: FIG. 1B is a lateral side view of the ultrasonic probe shown in FIG. 1A; FIGS. 2, 3, and 4 are sectional views showing ultrasonic probes, useful for understanding the theory on which the present invention relies; FIG. 5 is a sectional view. similar to FIG. 1. illustrating an alternative embodiment of the ultrasonic probe of the present invention; FIG. 6 is a perspective view exemplifying an array of the ultrasonic probe in accordance with the present invention; FIGS. 7A and 7B are a sectional view and a lateral view. similar to FIGS. 1A and 1B, respectively, showing another alternative embodiment of the present invention; FIG. 8 is a graph plotting frequency characteristics of the embodiment of the present invention; FIG. 9 is a sectional view illustrating a specific construction of the ultrasonic probe of the present invention: FIG. 10 is a graph showing characteristics of a reflector of the ultrasonic probe shown in FIG. 9; FIG. 11 is a sectional view. similar to FIG. 9. illustrating a specific construction of an alternative embodiment of the present invention; FIG. 12 is a graph, similar to FIG. 10, showing characteristics of an acoustic matching plate of the probe shown in FIG. 11; FIGS. 13 and 14 are perspective views, similar to FIG. 6, illustrating appearances of array types of probe of other alternative embodiments of the present invention; and FIGS. 15 and 16 are schematic block diagrams showing the illustrative embodiments of an ultrasonic diagnostic apparatus using the ultrasonic probe in accordance with the present invention. DESCRIPTION OF THE PREFERRED EMBODIMENTS Referring to FIG. 1A, an ultrasonic probe 200 in an illustrative embodiment includes, on the side of a load 100 with respect to a generally circular flat-shaped piezoelectric transducer material 10, an acoustic matching layer 20 with an electrode 12 interposed inbetween, and, on the opposite side, an annular layer of acoustic reflecter 50 and a backing material 30 with an electrode 11 interposed therebetween. The ultrasonic probe 200 is an electric acoustic transducer which transmits ultrasonic waves in response to a frequency voltage applied between the electrodes 11 and 12 and generates frequency voltage between the electrodes 11 and 12 in response to the received ultrasonic waves. The load 100, which is conceptionally indicated with an arrow, is a subject for an ultrasonic diagnosis, such as a living body. As seen in FIG. 1B, brought into contact with the generally circular flat-shaped electrode 11 are the annular acoustic reflecting layer 50 on the circumferential area B and the backing material 30 near the center area A. In addition, assuming that acoustic impedances are represented by Z₁₀ for the transducer material 10, Z₃₀ for the backing material 30, and Z₅₀ for the acoustic reflecting layer 50, respectively, they become in the relation of Z₃₀<Z₁₀, Z₅₀>Z₁₀. Specifically, the backing material 30 is a layer of backing material having an acoustic impedance lower than that of the piezoelectric material 10, whereas the acoustic reflecting layer 50 is a layer of backing material having an acoustic impedance higher than that of the piezoelectric material 10. If so structured, the center area A and the vicinity thereof on the piezoelectric material 10 vibrate in a λ/2 resonance mode, while the circumferential area B does in a λ/4 resonance mode. Where, λ is an ultrasonic wavelength. Consequently, the probe 200, as a whole, in the vicinity of the center area A can transmit ultrasonic waves to the load 100 and receive the ultrasonic waves returned from the load 100 in the form of echoes at a frequency twice as high as that of the probe on the circumferential area B. In the meantime, the nature of the ultrasonic wave causes a transducer having a small aperture to exhibit a tendency that the higher the frequency becomes, the more the directivity increase. Now, assuming that a deviated angle of ultrasonic waves from the linear travel, i.e. a divergent angle, is ϑ , the relation between an aperture diameter D near the center area A and an ultrasonic frequency f is ϑ ∼ f x D. Therefore, when the ultrasonic frequency f is doubled, even if the aperture diameter D is half in size, the same directivity, i.e. the same divergent angle ϑ, can be obtained. Consequently, to obtain the most desirable example according to FIG. 1A, assuming that the diameter of the circumferential area B is D B and the diameter of the center area is D A , the acoustic reflecting layer 50 may be formed to be D B = 2 x D A . Subsequently, the theory of the ultrasonic probe 200 of the present invention will be described hereunder. making reference to FIGS. 2. 3, and 4. FIG. 2 is a sectional view illustrating an ultrasonic probe, called a λ/2 resonance probe, consisting of a generally circular. flat-shaped piezoelectric transducer material 70. an acoustic matching layer 60 having the same shape as that of the piezoelectric material 70. and a generally cylindrical backing material 90. The ultrasonic probe resonates at a frequency which satisfies a condition that. when the relation between the acoustic impedance Z₉₀ of the backing material 90 and the acoustic impedance Z₇₀ of the piezoelectric material 70 is Z₇₀>Z₉₀, the thickness of the piezoelectric material 70 is equal to 1/2 of the wavelength λ, and has the central frequency f with a certain narrow bandwidth f ±Δf. In this case. the acoustic impedance Z₆₀ of the acoustic matching layer 60 is set to be a value falling between the acoustic impedance Z₇₀ of the piezoelectric material 70 and the acoustic impedance Z₁₀₀ of the load (the subject) 100. Specifically. it is selected in the range of Z₇₀>Z₆₀>Z₁₀₀ to be ordinarily set to a λ₁₀₀/4. Where. a λ₆₀ is a wavelength involved in the acoustic matching layer 60, and let the acoustic velocity in the acoustic matching layer 60 be C₆₀, the relation is λ= C₆₀/f. FIG. 3 is a sectional view illustrating the ultrasonic probe called a λ/4 resonance probe. The ultrasonic probe shown in FIG. 3 differs from the one shown in FIG. 2 in that the piezoelectric material 75 is half as thick as the piezoelectric material 70 shown in FIG. 2. Specifically, the piezoelectric material is set to the λ/4 resonance. Further, between the backing material 93 and the transducer material 75 there exists an acoustic reflecting layer 80, the acoustic impedance Z₈₀ of which is selected to be Z₈₀>Z₇₅. The backing material 93 is a member for supporting the acoustic reflecting layer 80. Consequently, the ultrasonic probe shown in FIG. 3 also has the same resonant frequency f as that of the ultrasonic probe shown in FIG. 2. As stated above, the λ/4 resonance mode probe can transmit and receive ultrasonic waves having the same frequencies, using a transducer which is half as thick as that used in the λ/2 mode. Thus, where, as in the case of high molecular piezoelectric material, it is impossible to form such a thick transducer due to difficulty in manufacturing, the λ/4 resonance mode is often employed. On the contrary, where, as in the case of a ceramic piezoelectric transducer, it is impossible to manufacture such a thin transducer, the λ/2 resonance mode is more advantageously adopted. In summary, as clearly seen in the comparison of FIGS. 2 and 3, even though the thickness of the piezoelectric transducer materials are the same, the case of the λ/2 resonance mode and the case of the λ/4 resonance mode which has on the back surface of the acoustic reflecting layer 85 an acoustic impedance higher than that of the piezoelectric material differ completely from each other in respect of the resonant frequency. In the λ/2 resonance mode the piezoelectric material resonates at a frequency twice as high as that in the λ/4 resonance mode to transmit and receive ultrasonic waves. The illustrative embodiment of the present invention shown in FIG. 1 is a combination of the structures shown in FIGS. 2 and 4 to form the acoustic reflecting layer 85 shown in FIG. 4 into an annular shape as shown in FIG. 1A. FIGS. 5 and 6 show alternative embodiments of the ultrasonic probe involved in the present invention. An illustrative embodiment shown in FIG. 5 relates to an acoustic matching layer 20a, wherein the circumferential area B for the λ/4 resonance mode is formed to be twice as thickly as the center area A for the λ/2 resonance mode to accomplish good transmission of frequencies having longer wavelength in the circumferential area B and frequencies having shorter wavelength in the center area A and the vicinity thereof. An illustrative embodiment shown in FIG. 6 is an array type of ultrasonic probe, wherein piezoelectric transducers 10a are arranged in the form of a linear array. In the direction perpendicular to the scanning direction S-S, i. e. the longitudinal direction toward the respective transducers 10a, provided on the center portion A of the back surface are backing materials, not shown, and formed on the back surface near both of the edge portions B are acoustic reflecting layers 50a. The piezoelectric transducers 10a, the backing materials, and the acoustic reflecting layers 50a have similar functions to those of the piezoelectric material 10, the backing material 30, and the acoustic reflecting layers 50, respectively, while their shapes are not cylindrical but generally rectangular as shown in the figure. To avoid complexity in FIG. 6, a backing material is not shown. Further, the acoustic matching layer 20a, similar to an embodiment shown in FIG. 5, is designed to have such a thickness that the more central portions of the matching layer 20a can better transfer the ultrasonic waves of higher frequency. An array type ultrasonic probe shown in FIG. 6. in the longitudinal direction toward the respective transducers 10a, can transmit and receive near the center portion A frequencies being twice as high as those near both edge portions B. For example. when a probe is so designed as to selectively resonate near both end portions B at the frequency of 3.5 MHz which has been mainly used so far for the abdomen of the human body. in the vicinity of the center portion A the probe can obtain a doubled resonant frequency as high as 7 MHz which is effective for diagnosis of the shallower regions of the living body. such as the mammary gland, etc. In FIGS. 7A and 7B. there are shown alternative embodiments of the ultrasonic probe 200 of the present invention. comprising a generally disc-shaped piezoelectric material 10. In the figures. similar components or structural elements are designated by the same reference numerals. and redundant description will be avoided for simplicity. Provided on one main surface of the piezoelectric material 10 is an electrode 12 brought in contact with an acoustic matching layer 20. Provided on the other main surface is an electrode 11 supported by a backing material 30 which, in the illustrative embodiment of the present invention, includes an acoustic reflecting layer 50b. The piezoelectric material 10 is an electric acoustic transducer material which. in response to an electric signal applied between both electrodes 11 and 12. generates ultrasonic waves and. in response to the ultrasonic waves received thereby, generates an electrical signal associated therewith. The acoustic reflecting layer 50b has a plane surface on the adjacent side of the piezoelectric material 10, while in the direction of receiving ultrasonic waves T-R the surface is not flat but forms a concave surface so as to make the thickness gradually thinner from the circular peripheral portion toward the center portion. As previously stated, if without using the acoustic reflecting layer 50b the backing material 30 should be acoustically connected directly to the piezoelectric material 10, the piezoelectric material 10 would be in the λ/2 resonance mode. In the illustrative embodiment, however, as the acoustic reflecting layer 50b has been provided in the manner as stated above, the piezoelectric material 10 has the λ/4 resonance mode. The fact that when the thickness of the acoustic reflecting layer 50b is continuously varied, the resonant frequency of the piezoelectric material 10 varies accordingly has been recognized by the detailed simulation in the literatures published by the inventors and their group; K. Yamaguchi et al "New Method of Time Domain Analysis of the Performance of Multi-Layered Ultrasonic Transducers" IEEE Trans. on Ultra. Ferro. and Freq. Cont. Vol. UFFC-33. No. 6 (Nov. 1986). In the illustrative embodiment of the present invention, the probe 200 is constructed in a method according to the literatures. FIG. 8 plots the properties of the probe. It is understandable that when the thickness of the acoustic reflecting layer 50b is varied in a range of 0 - 0.4 λ ob, the resonant frequency of the piezoelectric material 10 varies in a range of fo -fo/2. Where, λ ob is a wavelength of the frequency fo included in the acoustic reflecting layer 50b and is representative of a case where the acoustic impedance ratio Z₅₀/Z₁₀ for the acoustic reflecting layer 50b and the piezoelectric material 10 is equal to 4. In addition, the acoustic impedance and the thickness of the acoustic matching layer 20 have been selected to establish the maximum sensitivity. In this case, however, the sensitivity is based on the definition given in the literatures previously listed. Based on the results of analysis shown in FIGS. 7A and 8, an illustrative embodiment of the ultrasonic probe 200 is shown in FIG. 9. In the figure, the same reference numerals as those shown in FIG. 7 are used for indicating similar elements. Also, the sectional view of the acoustic reflecting layer 50b is shown in FIG. 10. In the illustrative embodiment, the central frequency fo is 7.5 MHz, the reflecting material 50 uses a copper (Cu) plate (Vb=5000m/s, Zb=45x10⁶ kg/m²s), and a sectional shape, when Zt/Zb=4, toward the radial direction from fo (the center portion) is shown. As seen in the figure, since the thickness of the reflecting layer 50 has been designed to be gradually thinner from the circumferential portion toward the center portion, the resonant frequency is, according to the thickness, distributed in a range of 7.5 - 3.75 MHz. FIG. 11 shows an embodiment in which the maximum sensitivity is provided for the probe 200 illustrated in FIG. 9. By forming the acoustic matching layer 20b into a sectional shape as shown in FIG. 12 and selecting resin (Vm=2500m/s, Zm= 3x10⁶ kg/m²s) for the material, the maximum sensitivity can be obtained. In other word, in the illustrative embodiment the thickness in the frontal direction of the acoustic matching layer 20b has been formed to be linearly thinner from the circumferential portion of the piezoelectric material 10 toward the center portion thereof. FIG. 13 shows an illustrative embodiment in which the present invention has been applied in an array type of probe. In the ultrasonic beam scanning direction S-S. provided on both surfaces of the bodies of piezoelectric material 10 are an acoustic matching layer 20c and a reflecting layer 50c as shown in the figure. The illustrative embodiment is similar to that shown in FIG. 9 except that the reflecting layer 50c formed into a concave shape and extending in the longitudinal direction of the array causes the bodies of piezoelectric material 10c to resonate in the resonance mode of λ/2 - λ/4. This effectively enables ultrasonic survey in various depths to be executed. Ultrasonic beam is transmitted and received in an arrowed direction R - T. In FIG. 14. the array type probe shown in FIG. 13 is provided with the reflecting layer 50c splitted to be associated with the respective piezoelectric bodies 10c. As seen in the figure. the reflecting layer 50c can be easily manufactured and an array type probe in a disirable size may be designed. As described so far. in accordance with the embodiments of the present invention, since the thickness of the reflecting plate is different over the entire area thereof. an ultrasonic probe may be provided and easily manufactured in which the resonance modes are. without being confined to resonant frequencies specific to respective transducers. continuously distributed in a range of λ/2 - λ/4. In addition. the present invention is applicable effectively to ultrasonic probes of other types. such as a linear array type of probe, a sector type of probe. a convex type of probe. etc. FIGS. 15 and 16 show illustrative embodiments of an ultrasonic diagnostic apparatus including an ultrasonic probe embodied by the present invention. In FIG. 15, a probe 200 has two resonant frequencies f and 2f connected to transmitters 300 and 350, respectively. The transmitters 300 and 350 are circuits for forming either of two resonant waveforms included in the probe 200. The apparatus comprises an operation console 800 used for receiving operator instructions from an operator to generate operation signals associated therewith for, specifically, selecting in response to an input operation by the operator either of the frequencies f and 2f which is suitable for examining a subject region, for example. The operation console 800 is connected to a main control 900 which, according to an operation command received by the operation console 800, controls operations of the respective circuits included in the apparatus. For example, when a frequency is selected on the operation console 800, the main control 900 causes the transmitters 300 and 350 associated with that frequency to operate. As a result, from the probe 200 ultrasonic waves having the selected frequency are transmitted. Also, connected to the probe is a receiver 400 which is a circuit for receiving an echo from a subject to be examined. The receiver 400 is connected to an analog-to-digital (A/D) converter 500 which is a circuit for converting signals received in the receiver 400 into associated digital signals. The digital signals are in turn stored in a memory 600, and data stored in the memory 600 are developed in the form of a tomographic image on a display 700. The receiver 400 may be implemented in the form of a broad-banded circuit having a receiving characteristic agreeable to the couple of frequencies f and 2f. For an alternative means, two discrete receiver agreeable to both frequencies may be prepared to use, in response to a command from the main control 900, for selecting one of the circuits having the frequency characteristics suitable to both receivers. The illustrative embodiment shown in FIG. 16 has a plurality of memories 600. 650. and 680 to obtain tomographic images having the respective frequencies and compositely process those tompgraphic images for display. In operation, firstly the transmitter 300 is driven to cause the probe 200 to transmit ultrasonic waves having a frequency f . and then over the receiver 400 and the A/D transducer 500 tomographic data of the deeper regions of a subject are stored in the memory 600. Similarly. the transmitter 350 is driven to cause the probe 200 to transmit ultrasonic waves having the other frequency 2f. and then the receiver 400 captures tomographic data of the shallower regions of the subject to store it in the memory 650 through the A/D transducer 500. Subsequently. the two kinds of tomographic data stored in the memories 600 and 650 are compounded into a complete set of tomographic data. and resultant data will be stored in the memory 680 later on to be developed on the display 700. In this way. for the shallower regions tomographic images are collected in terms of echoes having a higher frequency 2f while for the deeper regions in terms of echoes having a lower frequency f to obtain tomographic images having respective frequencies suitable to the depths of the regions of the subject of interest. By compounding those tomographic images, a single tomographic image will be developed on the display 700. In addition. it is a matter of course that the present invention. without being restricted by the aforementioned embodiments. may be changed or modified variously within the scope and spirit of the present invention. In the illustrative embodiments, included in the circumferential area is an acoustic reflecting layer having a higher acoustic impedance and included in the center area and the vicinity thereof is a backing material having a lower acoustic impedance, for example, while the probe may not be divided into the central and circumferential areas but into right and left half areas, for example. Further, similar to the illustrative embodiment shown in FIG. 16, when respective tomographic images are compounded to be developed on a display, the display field may be divided or the field may be provided with a window to display both of the tomographic images side by side or in the form of an overlapped, single image. Still further, for storing data of tomographic images three memories are included in the structure shown in the illustrative embodiment, while the apparatus may be adapted to include a couple of image memories in which one of the pair of image data is written over the other to obtain a single tomographic image. Alternatively, when a single memory is adapted to store data first, followed by arithmetic processing executed with the data thus stored to obtain a single tomographic image. As clearly read in the description so far, in accordance with the present invention, a single ultrasonic probe has a backing body provided for a piezoelectric transducer material and acting as part of the load, and improved into a specific arrangement to establish both of λ/2 and λ/4 resonance modes exsisting simultaneously. This enables the ultrasonic probe to be easily manufactured and implemented to include therein a broad frequency band with improved characterisitcs. Yet, ultrasonic tomographic images will be obtained with a good resolution and a good S/N ratio over a variety of depths in a subject to be studied. Further in accordance with the present invention, since a single unit of ultrasonic probe can obtain a tomographic image having two different frequencies, the use of the characteristical difference of echoe signals to different frequencies makes it possible to execute processing. such as tissue characterization (TC). Also. attenuation coefficient of tissue can be obtained. for example. Consequently, discrimination between normal and abnormal tissue including cancer tissue becomes possible. Still further. in accordance with the present invention. by designing a backing material or a reflecting material of a transducer to have uneven thickness. an ultrasonic probe capable of transmitting and receiving ultrasonic waves having a broad bandwidth in the resonance mode from a λ/2 mode to a λ/4 mode can be realized. As a result. in all the depths of a subject to be diagnosed an ultrasonic tomographic image having high resolution and S/N ratio can be obtained. Besides. the probe has comparatively less difficulties in manufacture and a wide range of applications. While the present invention has been described with reference to the particular illustrative embodiments. it is not to be restricted by those embodiments but only by the appended claims. It is to be appreciated that those skilled in the art can change or modify the embodiments without departing from the scope of the appended claims.

Claims: An ultrasonic diagnostic apparatus comprising: transmission means (300, 350) for generating a frequency voltage having a plurality of frequencies and for feeding the frequency voltage to an ultrasonic probe (200); said ultrasonic probe (200) being provided for generating ultrasonic waves in response to the frequency voltage and electric signals in response to received ultrasonic waves; said ultrasonic probe (200) comprising: a layer of piezoelectric material (10, 10a, 10c) having generally flat main surfaces; a pair of electrodes (11, 11a, 11c, 12, 12a, 12c) provided on the flat main surfaces of said layer of piezoelectric material (10, 10a, 10c) to apply the frequency voltage to said layer of piezoelectric material (10, 10a, 10c); a layer of backing material (30) provided on one (11, 11a, 11c) of said pair of electrodes (11, 11a, 11c, 12, 12a, 12c) and having an acoustic impedance lower than that of said layer of piezoelectric material (10, 10a, 10c); and a layer of reflecting material (50, 50a, 50b, 50c) interposed between said one electrode (11, 11a, 11c) and said layer of backing material (30) and having an acoustic impedance higher than that of said layer of piezoelectric material (10, 10a, 10c); said layer of reflecting material (50, 50a, 50b, 50c) including a first portion forming a center portion and a second portion forming a peripheral portion of said first portion so as to transmit wideband ultrasonic waves in a range of λ/2 to λ/4 resonant modes, said first portion having a thickness thinner than that of said second portion including a zero thickness; receiver means (400, 500) for receiving the electric signals from said ultrasonic probe (200); image visualizing means (600, 650, 680, 700, 900) for producing images represented by the electric signals received by said receiver means (400, 500); said image visualizing means (600, 650, 680, 700, 900) comprising: image combining means (600, 900) for combining the images represented by the electric signals; and image display means (700) for visualizing the combined images. An ultrasonic diagnostic apparatus in accordance with claim 1, wherein the first and second portions have a thickness continuously varying all over both the portions. An ultrasonic diagnostic apparatus in accordance with claim 1, wherein the second portion has a substantially zero thickness to allow said layer of backing material (30) to be in partial contact with said one electrode (11). An ultrasonic diagnostic apparatus in accordance with claim 1, wherein said layer of piezoelectric material (10, 10a, 10c), said pair of electrodes (11, 12), and said layer of reflecting material (50, 50a, 50b, 50c) have a generally circular flat shape, said layer of backing material (30) having a generally cylindrical shape. An ultrasonic diagnostic apparatus in accordance with claim 1, wherein said ultrasonic probe comprises a layer of acoustic matching material (20) formed on another (12) of said pair of electrodes (11, 12), and having a substantially uniform thickness. An ultrasonic diagnostic apparatus in accordance with claim 1, wherein said ultrasonic probe (200) comprises a layer of acoustic matching material (20a, 20b) formed on another (12) of said pair of electrodes (11, 12), and including a periphery portion and a center portion which is thinner than the periphery portion. An ultrasonic diagnostic apparatus in accordance with claim 1, wherein said ultrasonic probe comprises a plurality of ultrasonic probes arranged in the form of an array, said layer of piezoelectric material (10a, 10c) has a generally rectangular shape and generally flat main surfaces opposite to each other. An ultrasonic diagnostic apparatus in accordance with claim 3, wherein the diameter of the second portion of the reflecting material is substantially half that of the whole layer of reflecting material (50a). An ultrasonic diagnostic apparatus in accordance with claim 1, wherein said transmission means (300, 350) comprises a plurality of transmitters, each of which generates an electric signal at one different frequency of the plurality of frequencies. An ultrasonic diagnostic apparatus in accordance with claim 1, wherein said image visualizing means (600, 650, 680, 900) comprises: a plurality of first storage means (600, 650), each of which stores therein electric signals representative of images associated with different one of the plurality of frequencies; second storage means (680), interconnected to said plurality of first storage means (600, 650) for storing therein electric signals representative of an image, into which images represented by the electric signals stored in said plurality of first storage means (600, 650) are combined; control means (900), interconnected to said plurality of first storage means (600, 650) and said second storage means (680), for storing in said second storage means (680) electric signals representative of said image combined with images represented by the electric signals stored in said plurality of first storage means (600, 650); and image display means (700), controlled by said control means (900), for reading electric signals out of said second storage means (680) to develop the combined image.

Inventors: FUJII TADASHI C O TERUMO KABUS, YAGAMI HIROYUKI C O TERUMO KAB, FUJII, TADASHI, C/O TERUMO KABUSHIKI KAISHA, YAGAMI, HIROYUKI, C/O TERUMO KABUSHIKI KAISHA
Applicants: TERUMO CORP, TERUMO KABUSHIKI KAISHA
Application year: 1990
Main classification: G01N29
IPC codes: B06B1