CA1212448A - Selectable focus sphericone transducer, imaging apparatus and switching means - Google Patents
Selectable focus sphericone transducer, imaging apparatus and switching meansInfo
- Publication number
- CA1212448A CA1212448A CA000432763A CA432763A CA1212448A CA 1212448 A CA1212448 A CA 1212448A CA 000432763 A CA000432763 A CA 000432763A CA 432763 A CA432763 A CA 432763A CA 1212448 A CA1212448 A CA 1212448A
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- ultrasonic transducer
- transducer assembly
- piezoelectric material
- focus
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Abstract
SELECTABLE FOCUS ULTRASONIC TRANSDUCERS
FOR DIAGNOSTIC IMAGING
Abstract of the Disclosure Dual focus ultrasonic transducers are provided having an effective aspheric radiating surface. The transducers exhibit an elongated focal zone in which the radiated ultrasonic energy is concentrated. An annular groove separates the piezoelectric material into an inner disc region and an outer annular region for simultaneous activation or activation of the inner disc alone. When the focus is switched, both the near field limit and the geometric focus are changed to provide near and far focal zones of good lateral resolution. The focus is changed by a reed switch connection to the two transducer regions, which permits proximity switch control of the transducer operation in a shielded environment for good noise performance.
FOR DIAGNOSTIC IMAGING
Abstract of the Disclosure Dual focus ultrasonic transducers are provided having an effective aspheric radiating surface. The transducers exhibit an elongated focal zone in which the radiated ultrasonic energy is concentrated. An annular groove separates the piezoelectric material into an inner disc region and an outer annular region for simultaneous activation or activation of the inner disc alone. When the focus is switched, both the near field limit and the geometric focus are changed to provide near and far focal zones of good lateral resolution. The focus is changed by a reed switch connection to the two transducer regions, which permits proximity switch control of the transducer operation in a shielded environment for good noise performance.
Description
I
SELECTABLE FOCUS ULTRASONIC TRANSDUCERS
FOR DIAGNOSTIC IMAGING
-This invention relates to ultrasonic transducers for diagnostic imaging and, in particular, to transducers of a novel geometric design with variable focal ranges and reduced side lobe patterns.
Ultrasonic transducers are used in ultrasonic diagnostic systems to transmit waves of ultrasonic energy into a patient's body. Tissue interfaces in the body reflect some of this energy back toward the transducer in the form of echoes. The echoes are received by the transducer and converted into electrical signals. These signals may be processed by associating them with their times of arrival to reconstruct an image of the tissue or make fluid flow measurements.
In many applications of ultrasound it is desirable to be able to focus the waves or beams of ultrasonic energy at a particular tissue depth. Such focusing permits the reconstruction of images of good lateral resolution at a particular tissue depth of interest, for instance.
Focusing may be done in the signal processing, as in the case of phased arrays, or may be provided by the geometric shape of the transducer. Geometric focusing advantageous-lye eliminates much electrical complexity usually required to achieve the same result in the signal processing section of the system. Louvre geometric focal kirk-teristics are idealized normally for only a single focal point or line of focal points, which restricts the range of good image resolution This restriction has been overcome ho transducers having selectable geometric focal characteristics. A selectable focus transducer is shown in ITS Patent 4,138,895. The transducer there shown comprises a disc divided into a center electrode region and an annular electrode region.
A user can select just the center electrode for a large depth of focus, or the central and annular regions together for a smaller depth of focus. An acoustic lens provides the transducer arrangement with the desired aperture with point focal characteristics.
Another important characteristic of transducers are side lobe patterns. Transducers, like antennas, have transmissive characteristics that can be ar,aly~ed in terms of main and side lobes. It is desirable in general to have small side lobes for an ultrasonic transducer, since large side lobes can result in the reception and introduction of noise in a reproduced ultrasound image.
It is desirable, then, for an ultrasonic transducer to have good geometric focal characteristics which are adjustable so as to provide good resolution over a range of tissue depths. It is further desirable to reduce the transducer side lobe patterns so as to minimize noise in the reproduced image.
In accordance with the principles of the present invention, an ultrasonic transducer assembly is provided having a novel geometric focal characteristic. The transducer or transducer and lens arrangement resembles a concave spherical surface with opposite sides relative to the center of the surface canted toward each other in a semi-conical spheric configuration. The geometric focal characteristic thus provides a concentration of ultrasonic energy over a particular range of interest.
In accordance with a preferred embodiment of the present invention, the transducer material is divided into a center disc and an annular ring. When the center disc is activated, the range of optimal focus is located a relatively short distance from the transducer. When both the center disc and annular ring are activated, the range of optimal focus is located at a relatively greater distance from the transducer.
In accordance with a further aspect of the present invention, side lobes of a transducer of the present invention are reduced by anodization, wherein damping material is located at the outer periphery on the back of the transducer.
In accordance with yet another aspect of the present invention, a proximity switch is provided in the transducer assembly to switch between the long and short focal ranges. In order to prevent the introduction of noise into the received echo signals, the transducer electronics including the switch contacts are surrounded by a continuous shield. In a preferred embodiment of the present invention the proximity switch comprises a reed switch which is controlled by a magnet located external to the shield. The use of a proximity switch such as a reed switch thus permits the focal ranges to be switched without physically interrupting the shield and hence impairing the noise characteristic of the transducer assembly.
In the drawings:
FIGURE lo and lb illustrate idealized aperture and lobe patterns for a conical surface transducer;
- -FIGURES pa and 2b illustrate idealized aperture and lobe patterns for a spherical surface transducer;
FIGURES pa and 3b illustrate idealized aperture and lobe patterns for a transducer constructed in accordance with the principles of the present invention;
FIGURES I, 5, and 6 illustrate different embodiments of transducers constructed in accordance with the principles of the present invention;
FIGURES pa, 7b, and 7c illustrate idealized dual aperture spherical, conical and spheric transducers; and FIGURE 8 is an assembly drawing of a transducer probe constructed in accordance with the principles of the present invention.
Referring first to FIGURE lay a conical transducer is shown in cross-section. The transducer includes a conical surface 12 of piezoelectric ceramic material on a backer 10. The conical transducer exhibits an idealized aperture outlined at 16, which comprises a line of geometric focal points I emanating from the center of the transducer.
Conical transducers are advantageous in that they exhibit a narrow region of sharply defined focal points. Their disadvantage is that the energy emitted by the conical surface is relatively evenly distributed over the line of focal points. It would be desirable to be able to concentrate the emitted energy in a particular region of the aperture, so as to improve the sensitivity of the transducer at a particular tissue depth of interest.
FIGURE pa illustrates a spherical transducer in cross-section. This transducer includes a spherical surface 22 I I
of piezoelectric material mounted on a backer 20. The spherical transducer exhibits an idealized aperture outlined at 26, which contains a single seornetric focal point 240 The ultrasonic energy emitted from the spherical surface of the transducer 22 converges at this point, and diverges beyond it. The spherical transducer is capable of producing sharply focused images of tissue in the vicinity of the geometric focal point 24 by reason of the concentrated ultrasonic energy at the point.
However, the aperture is only sharply focused at one point, with resolution degrading at regions removed from this point.
A transducer constructed in accordance with the principles of the present invention is shown in cross-section in FIGURE pa. The transducer there shown is neither conical nor spherical, but exhibits many of the advantages of these two transducer types while overcoming several of their shortcomings. The novel transducer of FIGURE pa includes an aspherie surface 32 of piezoelectric material mounted on a backer 30. The shape of the surface 32 is difficult to visualize in three dimensions, but in two dimensional cross-seetion it resembles a spherical surface transducer which has been bent at the center point I
The halves of the spherical surface on either side of the center point appear to be folded toward each other. The transducer exhibits the idealized aperture outlined at 36, in which most of the emitted ultrasonic energy is focused at points 34 in an elongated focal region. Unlike the conical and spherical transducers, the ultrasonic energy emitted by the novel transducer is neither focused along the entire center line of the transducer, nor is it focused at a single point. Rather, it is concentrated in an elongated region of optimal focus in which tissue of a significant depth can be imaged with good lateral I
resolution. The elongated region in a constructed embodiment of the present invention can extend over a six to seven centimeter depth for a 19 mm, 3.5 MHz -trays-dicer.
Different embodiments of transducers constructed in accordance with the principles of the present invention are shown in FIGURES 4, 5 and 6. In FIGURE 4, an spheric surface piezolectric element 300 includes a central area 312 which is electrically separate from an outer annuls 314. The piezoelectric material is mounted in a cylindrical mount 306. The inner area 312 may be activated alone or a switch 316 may be closed to activate both areas 312 and 314 simultaneously to focus the transducer over different depths of focus. The concave front of the transducer 300 is filled in with an epoxy material to provide a flat face 302 on the transducer.
A preferred embodiment of the present invention is shown in FIGURE 5. In this embodiment the piezoelectric material exhibits a conical shape, and contains an annular groove which divides the material into an inner conical region 212 and an annular outer region 214. Tune center region 212 may be activated alone or together with the annular region 214 by closing a switch 216. When the switch 216 is open the center region 212 will focus in the near field out to a point 218 at approximately 9 centimeters 7 and when the two regions are activated together, far field focusing is effected out to a point 201 at approximately 14 centimeters.
On the face of the piezoelectric material is an acoustic lens having a spherical face 210. The combination of the conical piezoelectric material 212, 214 and the spherical faced lens provide the spheric aperture characteristic of the embodiments of FIGURES pa and 4. The concave lens is again filled in with epoxy to provide a flat face 20 on the transducer. In a constructed embodiment of FIGURE 5, the acoustic lens 210 was composed of a high acoustic impedance and velocity epoxy materiel, and the filler material at 208 was a lower acoustic impedance and velocity epoxy material. The conical piezoelectric transducer 212, 214 and the spherical acoustic lens provide the desired elongated focal region aperture, and the filler 20~ forms a simple plano-convex lens which extends the focal zone to point 201. It follows from the principles of this embodiment that an spheric transducer could also be made utilizing a spherical piezoelectric disc and a conical faced lens.
The embodiment of FIGURE 5 is more easily manufactured than the other illustrated embodiments of the present invention. This is because a conical ceramic transducer can be readily manufactured and the spherical acoustic lens can be formed by a simple lapping technique. The embodiment of FIGURE I with its spheric ceramic surface, should be formed by grinding the ceramic material with a precise, numerically controlled lathe, for example.
The embodiment of FIGURE 6 is composed of a flat disc 400 of piezoelectric material, including a central disc 404 and an annular ring 406, the activation of which is controlled by a switch 416. The disc 400 is fronted with an acoustic lens 402 having an spheric surface. This combination of piezoelectric material and spheric lens will produce the same aperture as the embodiments of FIGURES 4 and 5.
It is desirable for a transducer to exhibit a radiation/
reception pattern with reduced side lobes, since signals received from the side lobe regions can introduce noise I
which will degrade image quality. A conical transducer such as that shown in FIGURE lo will exhibit a lobe pattern as shown in FIGURE lb, with a large main lobe I
and sizable side lobes I and I The large swaddles I
5 and I are undesirable in an ultrasonic diagnostic system.
The spherical transducer of FIGURE pa will exhibit a more acceptable lobe pattern as shown in FIGURE 2b. The pattern there shown includes a large main lobe 50 and small side lobes 52, 52'.
The spheric transducer of the present invention will exhibit a love pattern intermediate those of FIGURES lb and 2b. The lobe pattern of a transducer of the present invention is improved in accordance with a further aspect of the present invention by providing backing material around the outer perimeter of the transducer as shown at 304 in FIGURES 4 and 5. This ring of backing material damps vibrations at the outer perimeter of the piezoelectric material thereby reducing the energy radiated from the perimeter of the piezoelectric material.
For the dual focus, two area transducers of FIGURES 4 and 5, the ring of backing material may be extended to back the central region 212 or 312 to damp vibrations at the perimeter of the central region when it is operated alone.
This damping technique, generally referred to as anodizing, causes the transducer to be a non-uniform radiator, which "smears" the small side lobes of the transducer as shown in FIGURE 3b, which illustrates a large main lobe 60 and side lobes 62, 62', which are approximately the same size as the side lobes 52, 52' of the spherical transducer.
A comparison of idealized apertures of different dual focus transducers is shown in FIGURES pa, 7b and 7c.
FIGURE pa illustrates the focal pattern of a simple dual I, r aperture spherical transducer, including a central spherical region 120 and an outer annular region 122.
When both regions 120 and 122 of the transducer are activated simultaneously, the transducer exhibits an aperture outlined at 124, which narrows sharply at a focal region 1250 Focusing is ineffective beyond the near yield limit 129 of the transducer, which is approximately equal to the radius of the transducer squared divided by the wavelength of operation. The near field limit 129 is thus a linear function of the area of the transducer, which in this case is the total of both regions 120 and 122.
When the spherical transducer is switched to operate in the near field using only the center region 120, the aperture is as outlined by dotted lines 126. This aperture produces a focal region 127 closer to the transducer, with a near field limit at 123 by reason of the reduced area of the transducer. The aperture outlined at 126 does not narrow as sharply as the aperture outlined at 124, however, and the focal region 127 has a greater lateral dimension 1 than focal region 1250 This is because the focus is changed by changing the near field limit from 129 to 128; the geometric focus remains the same, generally located slightly beyond the far focal region 125.
FIGURE 7b illustrates the focal pattern of a simple dual aperture conical transducer having an inner conical surface 130 and an outer annular surface 132. When the inner conical surface 130 is activated alone, the energy from surface 130 focuses along the broken line shown at 137 and bounded by dotted lines 136. When both regions 130 and 132 are activated, the line of focal points is extended to include the points indicated at 135 as well as those at 137~ bounded by dashed lines 134. Switching from operation using both regions to operation using only the center region 130 reduces the near field limit, since the -10 ' transducer area changes, and also reduces the geometric focal length to only the focal points included in aperture outline 136. A line of distributed energy focal points is produced in both cases.
FIGURE 7c illustrates the focal pattern of a dual focus spheric transducer of the present invention When both the central region 140 and the outer annular region 142 of the transducer of FIGURE 7c are activated, a narrow focal region 145 is produced at the narrow portion of the aperture outlined by dashed lines 144. The area of the full transducer provides a near field limit indicated at 129.
When the transducer of FIGURE 7c is switched to operation using the central region 140 alone, the area of the transducer is reduced, which moves the near field limit to the line indicated at 128. But the geometric focus of the transducer also changes, since its effective radiating surface is spheric. Thus the aperture of the central region appears as outlined by dotted lines 146, containing a relatively narrow focal region 147. The focal region 147 is laterally narrower than region 127 of the spherical transducer by reason of the relocation of the geometric focus of the transducer to an area closer to the transducer. Good lateral resolution is therefore provided in both region 145 and region 147.
Since the geometric focus moves closer to the transducer when operation is switched from two region to central region operation, the diameter d' of the central region 140 can be made larger than the diameter d of the equivalent central region 120 of the spherical transducer of FIGURE pa. Several benefits result from use of a relatively larger central region. First, the larger region will transmit and receive more energy than a smaller region, thereby increasing the sensitivity of the transducer. Second, there is less of an impedance change when switchillg from double to single region operation, which makes the tuning electronics coupled to the transducer simpler. And third, the lurker central region 140 contributes to the narrowing effect on the aperture 1~6.
The ultrasonic transducer of the present invention is conveniently mounted in a probe assembly such as that shown in FIGURE 8. The probe assembly there shown advantageously provides an electrically shielded environment which reduces the tendency to pick up stray electronic interference. The probe assembly also provides a means for switching the focus of the transducer in a manner which does not interrupt the shielded environment.
As the focus of the transducer is switched, the tuning of the transducer is also changed and a signal is provided which indicates the selected focal characteristics.
The probe assembly of FIGURE 8 includes a forward plastic cylindrical section 150 with a closed acoustic window face 151. The spheric transducer 152 is located behind the window 151. Leads 156 extend from the separate regions of the transducer. The interior of the cylindrical section 150 is lined with a nonmagnetic shield 154 such as copper.
The rear portion of the cylindrical section 150 narrows to a smaller diameter as indicated by dividing ridge 157.
Two dimples shown at 158 are provided on the outside of the narrow portion which form a portion of the detent mechanism of the switch. The end 159 of the cylindrical section 150 is open.
A plastic ring 160 slides over the narrow portion of the cylindrical section 150 up to the ridge 157. On the Lo inner surface of the ring 160 is a small ball 162 which rides between the dimples 158 and snaps into them to provide a detent mechanism for the ring. A groove 168 is formed around the inner surface of the ring to hold a magnet 164 in a predetermined position relative to the ball bearing 162. A small pin 166 extends from the inner surface of the ring at the bottom of the ring.
With the ring 160 in place on the forward cylindrical section 150, a rear cylindrical section 170 slides over the remainder of the narrow portion of section 150. A
recessed collar 176 is then located under the ring 160.
The collar 176 has a slot 174 in it so that pin 166 can move from one end of the slot to the other as the ring 160 is turned. The pin and slot thereby provide a stop for the ring to permit the ring to be turned only through the arc of the slot.
Finally, the wires 156 from the transducer are soldered to a small printed circuit board 190, mounted on an of connector 180. The of connector 180 is inserted into the open end 159 of the section 150 up to the lip 181 of the connector. mounted on the connector at a plastic ring 182 are three reed switches 184, 136 and 188. The reed I switches are wired to the printed circuit board 190. When the connector is inserted in the section 150 in the proper position, the reed switches are located under either side of the arc traversed by the magnet 164 as the ring 160 is turned. When the ring is turned to one detent position the magnet 164 is located over reed switches 184 and 186 to close them. And when the ring is in its other detent position the magnet is located over reed switch 188 to close it. The of connector 180 and copper shield 154 provide a completely shielded cavity for the wiring, printed circuit board, switches, and board components in the inside of the section 150.
Turning the ring performs three switching functions in the probe assembly. First, the focal characteristics of the transducer are switched between short focus using only the central disc of the transducer, and long focus by connecting the central disc and annular ring of the transducer together to be activated simultaneously.
Second, the tuning of the circuitry on circuit board 190 is switched to match the respective electrical characteristics of the transducer in the two operating modes. Third a resistance value on the circuit board is changed to produce a signal indicative of the operating mode, which signal is coupled out through the connector along with signals to and from the transducer.
SELECTABLE FOCUS ULTRASONIC TRANSDUCERS
FOR DIAGNOSTIC IMAGING
-This invention relates to ultrasonic transducers for diagnostic imaging and, in particular, to transducers of a novel geometric design with variable focal ranges and reduced side lobe patterns.
Ultrasonic transducers are used in ultrasonic diagnostic systems to transmit waves of ultrasonic energy into a patient's body. Tissue interfaces in the body reflect some of this energy back toward the transducer in the form of echoes. The echoes are received by the transducer and converted into electrical signals. These signals may be processed by associating them with their times of arrival to reconstruct an image of the tissue or make fluid flow measurements.
In many applications of ultrasound it is desirable to be able to focus the waves or beams of ultrasonic energy at a particular tissue depth. Such focusing permits the reconstruction of images of good lateral resolution at a particular tissue depth of interest, for instance.
Focusing may be done in the signal processing, as in the case of phased arrays, or may be provided by the geometric shape of the transducer. Geometric focusing advantageous-lye eliminates much electrical complexity usually required to achieve the same result in the signal processing section of the system. Louvre geometric focal kirk-teristics are idealized normally for only a single focal point or line of focal points, which restricts the range of good image resolution This restriction has been overcome ho transducers having selectable geometric focal characteristics. A selectable focus transducer is shown in ITS Patent 4,138,895. The transducer there shown comprises a disc divided into a center electrode region and an annular electrode region.
A user can select just the center electrode for a large depth of focus, or the central and annular regions together for a smaller depth of focus. An acoustic lens provides the transducer arrangement with the desired aperture with point focal characteristics.
Another important characteristic of transducers are side lobe patterns. Transducers, like antennas, have transmissive characteristics that can be ar,aly~ed in terms of main and side lobes. It is desirable in general to have small side lobes for an ultrasonic transducer, since large side lobes can result in the reception and introduction of noise in a reproduced ultrasound image.
It is desirable, then, for an ultrasonic transducer to have good geometric focal characteristics which are adjustable so as to provide good resolution over a range of tissue depths. It is further desirable to reduce the transducer side lobe patterns so as to minimize noise in the reproduced image.
In accordance with the principles of the present invention, an ultrasonic transducer assembly is provided having a novel geometric focal characteristic. The transducer or transducer and lens arrangement resembles a concave spherical surface with opposite sides relative to the center of the surface canted toward each other in a semi-conical spheric configuration. The geometric focal characteristic thus provides a concentration of ultrasonic energy over a particular range of interest.
In accordance with a preferred embodiment of the present invention, the transducer material is divided into a center disc and an annular ring. When the center disc is activated, the range of optimal focus is located a relatively short distance from the transducer. When both the center disc and annular ring are activated, the range of optimal focus is located at a relatively greater distance from the transducer.
In accordance with a further aspect of the present invention, side lobes of a transducer of the present invention are reduced by anodization, wherein damping material is located at the outer periphery on the back of the transducer.
In accordance with yet another aspect of the present invention, a proximity switch is provided in the transducer assembly to switch between the long and short focal ranges. In order to prevent the introduction of noise into the received echo signals, the transducer electronics including the switch contacts are surrounded by a continuous shield. In a preferred embodiment of the present invention the proximity switch comprises a reed switch which is controlled by a magnet located external to the shield. The use of a proximity switch such as a reed switch thus permits the focal ranges to be switched without physically interrupting the shield and hence impairing the noise characteristic of the transducer assembly.
In the drawings:
FIGURE lo and lb illustrate idealized aperture and lobe patterns for a conical surface transducer;
- -FIGURES pa and 2b illustrate idealized aperture and lobe patterns for a spherical surface transducer;
FIGURES pa and 3b illustrate idealized aperture and lobe patterns for a transducer constructed in accordance with the principles of the present invention;
FIGURES I, 5, and 6 illustrate different embodiments of transducers constructed in accordance with the principles of the present invention;
FIGURES pa, 7b, and 7c illustrate idealized dual aperture spherical, conical and spheric transducers; and FIGURE 8 is an assembly drawing of a transducer probe constructed in accordance with the principles of the present invention.
Referring first to FIGURE lay a conical transducer is shown in cross-section. The transducer includes a conical surface 12 of piezoelectric ceramic material on a backer 10. The conical transducer exhibits an idealized aperture outlined at 16, which comprises a line of geometric focal points I emanating from the center of the transducer.
Conical transducers are advantageous in that they exhibit a narrow region of sharply defined focal points. Their disadvantage is that the energy emitted by the conical surface is relatively evenly distributed over the line of focal points. It would be desirable to be able to concentrate the emitted energy in a particular region of the aperture, so as to improve the sensitivity of the transducer at a particular tissue depth of interest.
FIGURE pa illustrates a spherical transducer in cross-section. This transducer includes a spherical surface 22 I I
of piezoelectric material mounted on a backer 20. The spherical transducer exhibits an idealized aperture outlined at 26, which contains a single seornetric focal point 240 The ultrasonic energy emitted from the spherical surface of the transducer 22 converges at this point, and diverges beyond it. The spherical transducer is capable of producing sharply focused images of tissue in the vicinity of the geometric focal point 24 by reason of the concentrated ultrasonic energy at the point.
However, the aperture is only sharply focused at one point, with resolution degrading at regions removed from this point.
A transducer constructed in accordance with the principles of the present invention is shown in cross-section in FIGURE pa. The transducer there shown is neither conical nor spherical, but exhibits many of the advantages of these two transducer types while overcoming several of their shortcomings. The novel transducer of FIGURE pa includes an aspherie surface 32 of piezoelectric material mounted on a backer 30. The shape of the surface 32 is difficult to visualize in three dimensions, but in two dimensional cross-seetion it resembles a spherical surface transducer which has been bent at the center point I
The halves of the spherical surface on either side of the center point appear to be folded toward each other. The transducer exhibits the idealized aperture outlined at 36, in which most of the emitted ultrasonic energy is focused at points 34 in an elongated focal region. Unlike the conical and spherical transducers, the ultrasonic energy emitted by the novel transducer is neither focused along the entire center line of the transducer, nor is it focused at a single point. Rather, it is concentrated in an elongated region of optimal focus in which tissue of a significant depth can be imaged with good lateral I
resolution. The elongated region in a constructed embodiment of the present invention can extend over a six to seven centimeter depth for a 19 mm, 3.5 MHz -trays-dicer.
Different embodiments of transducers constructed in accordance with the principles of the present invention are shown in FIGURES 4, 5 and 6. In FIGURE 4, an spheric surface piezolectric element 300 includes a central area 312 which is electrically separate from an outer annuls 314. The piezoelectric material is mounted in a cylindrical mount 306. The inner area 312 may be activated alone or a switch 316 may be closed to activate both areas 312 and 314 simultaneously to focus the transducer over different depths of focus. The concave front of the transducer 300 is filled in with an epoxy material to provide a flat face 302 on the transducer.
A preferred embodiment of the present invention is shown in FIGURE 5. In this embodiment the piezoelectric material exhibits a conical shape, and contains an annular groove which divides the material into an inner conical region 212 and an annular outer region 214. Tune center region 212 may be activated alone or together with the annular region 214 by closing a switch 216. When the switch 216 is open the center region 212 will focus in the near field out to a point 218 at approximately 9 centimeters 7 and when the two regions are activated together, far field focusing is effected out to a point 201 at approximately 14 centimeters.
On the face of the piezoelectric material is an acoustic lens having a spherical face 210. The combination of the conical piezoelectric material 212, 214 and the spherical faced lens provide the spheric aperture characteristic of the embodiments of FIGURES pa and 4. The concave lens is again filled in with epoxy to provide a flat face 20 on the transducer. In a constructed embodiment of FIGURE 5, the acoustic lens 210 was composed of a high acoustic impedance and velocity epoxy materiel, and the filler material at 208 was a lower acoustic impedance and velocity epoxy material. The conical piezoelectric transducer 212, 214 and the spherical acoustic lens provide the desired elongated focal region aperture, and the filler 20~ forms a simple plano-convex lens which extends the focal zone to point 201. It follows from the principles of this embodiment that an spheric transducer could also be made utilizing a spherical piezoelectric disc and a conical faced lens.
The embodiment of FIGURE 5 is more easily manufactured than the other illustrated embodiments of the present invention. This is because a conical ceramic transducer can be readily manufactured and the spherical acoustic lens can be formed by a simple lapping technique. The embodiment of FIGURE I with its spheric ceramic surface, should be formed by grinding the ceramic material with a precise, numerically controlled lathe, for example.
The embodiment of FIGURE 6 is composed of a flat disc 400 of piezoelectric material, including a central disc 404 and an annular ring 406, the activation of which is controlled by a switch 416. The disc 400 is fronted with an acoustic lens 402 having an spheric surface. This combination of piezoelectric material and spheric lens will produce the same aperture as the embodiments of FIGURES 4 and 5.
It is desirable for a transducer to exhibit a radiation/
reception pattern with reduced side lobes, since signals received from the side lobe regions can introduce noise I
which will degrade image quality. A conical transducer such as that shown in FIGURE lo will exhibit a lobe pattern as shown in FIGURE lb, with a large main lobe I
and sizable side lobes I and I The large swaddles I
5 and I are undesirable in an ultrasonic diagnostic system.
The spherical transducer of FIGURE pa will exhibit a more acceptable lobe pattern as shown in FIGURE 2b. The pattern there shown includes a large main lobe 50 and small side lobes 52, 52'.
The spheric transducer of the present invention will exhibit a love pattern intermediate those of FIGURES lb and 2b. The lobe pattern of a transducer of the present invention is improved in accordance with a further aspect of the present invention by providing backing material around the outer perimeter of the transducer as shown at 304 in FIGURES 4 and 5. This ring of backing material damps vibrations at the outer perimeter of the piezoelectric material thereby reducing the energy radiated from the perimeter of the piezoelectric material.
For the dual focus, two area transducers of FIGURES 4 and 5, the ring of backing material may be extended to back the central region 212 or 312 to damp vibrations at the perimeter of the central region when it is operated alone.
This damping technique, generally referred to as anodizing, causes the transducer to be a non-uniform radiator, which "smears" the small side lobes of the transducer as shown in FIGURE 3b, which illustrates a large main lobe 60 and side lobes 62, 62', which are approximately the same size as the side lobes 52, 52' of the spherical transducer.
A comparison of idealized apertures of different dual focus transducers is shown in FIGURES pa, 7b and 7c.
FIGURE pa illustrates the focal pattern of a simple dual I, r aperture spherical transducer, including a central spherical region 120 and an outer annular region 122.
When both regions 120 and 122 of the transducer are activated simultaneously, the transducer exhibits an aperture outlined at 124, which narrows sharply at a focal region 1250 Focusing is ineffective beyond the near yield limit 129 of the transducer, which is approximately equal to the radius of the transducer squared divided by the wavelength of operation. The near field limit 129 is thus a linear function of the area of the transducer, which in this case is the total of both regions 120 and 122.
When the spherical transducer is switched to operate in the near field using only the center region 120, the aperture is as outlined by dotted lines 126. This aperture produces a focal region 127 closer to the transducer, with a near field limit at 123 by reason of the reduced area of the transducer. The aperture outlined at 126 does not narrow as sharply as the aperture outlined at 124, however, and the focal region 127 has a greater lateral dimension 1 than focal region 1250 This is because the focus is changed by changing the near field limit from 129 to 128; the geometric focus remains the same, generally located slightly beyond the far focal region 125.
FIGURE 7b illustrates the focal pattern of a simple dual aperture conical transducer having an inner conical surface 130 and an outer annular surface 132. When the inner conical surface 130 is activated alone, the energy from surface 130 focuses along the broken line shown at 137 and bounded by dotted lines 136. When both regions 130 and 132 are activated, the line of focal points is extended to include the points indicated at 135 as well as those at 137~ bounded by dashed lines 134. Switching from operation using both regions to operation using only the center region 130 reduces the near field limit, since the -10 ' transducer area changes, and also reduces the geometric focal length to only the focal points included in aperture outline 136. A line of distributed energy focal points is produced in both cases.
FIGURE 7c illustrates the focal pattern of a dual focus spheric transducer of the present invention When both the central region 140 and the outer annular region 142 of the transducer of FIGURE 7c are activated, a narrow focal region 145 is produced at the narrow portion of the aperture outlined by dashed lines 144. The area of the full transducer provides a near field limit indicated at 129.
When the transducer of FIGURE 7c is switched to operation using the central region 140 alone, the area of the transducer is reduced, which moves the near field limit to the line indicated at 128. But the geometric focus of the transducer also changes, since its effective radiating surface is spheric. Thus the aperture of the central region appears as outlined by dotted lines 146, containing a relatively narrow focal region 147. The focal region 147 is laterally narrower than region 127 of the spherical transducer by reason of the relocation of the geometric focus of the transducer to an area closer to the transducer. Good lateral resolution is therefore provided in both region 145 and region 147.
Since the geometric focus moves closer to the transducer when operation is switched from two region to central region operation, the diameter d' of the central region 140 can be made larger than the diameter d of the equivalent central region 120 of the spherical transducer of FIGURE pa. Several benefits result from use of a relatively larger central region. First, the larger region will transmit and receive more energy than a smaller region, thereby increasing the sensitivity of the transducer. Second, there is less of an impedance change when switchillg from double to single region operation, which makes the tuning electronics coupled to the transducer simpler. And third, the lurker central region 140 contributes to the narrowing effect on the aperture 1~6.
The ultrasonic transducer of the present invention is conveniently mounted in a probe assembly such as that shown in FIGURE 8. The probe assembly there shown advantageously provides an electrically shielded environment which reduces the tendency to pick up stray electronic interference. The probe assembly also provides a means for switching the focus of the transducer in a manner which does not interrupt the shielded environment.
As the focus of the transducer is switched, the tuning of the transducer is also changed and a signal is provided which indicates the selected focal characteristics.
The probe assembly of FIGURE 8 includes a forward plastic cylindrical section 150 with a closed acoustic window face 151. The spheric transducer 152 is located behind the window 151. Leads 156 extend from the separate regions of the transducer. The interior of the cylindrical section 150 is lined with a nonmagnetic shield 154 such as copper.
The rear portion of the cylindrical section 150 narrows to a smaller diameter as indicated by dividing ridge 157.
Two dimples shown at 158 are provided on the outside of the narrow portion which form a portion of the detent mechanism of the switch. The end 159 of the cylindrical section 150 is open.
A plastic ring 160 slides over the narrow portion of the cylindrical section 150 up to the ridge 157. On the Lo inner surface of the ring 160 is a small ball 162 which rides between the dimples 158 and snaps into them to provide a detent mechanism for the ring. A groove 168 is formed around the inner surface of the ring to hold a magnet 164 in a predetermined position relative to the ball bearing 162. A small pin 166 extends from the inner surface of the ring at the bottom of the ring.
With the ring 160 in place on the forward cylindrical section 150, a rear cylindrical section 170 slides over the remainder of the narrow portion of section 150. A
recessed collar 176 is then located under the ring 160.
The collar 176 has a slot 174 in it so that pin 166 can move from one end of the slot to the other as the ring 160 is turned. The pin and slot thereby provide a stop for the ring to permit the ring to be turned only through the arc of the slot.
Finally, the wires 156 from the transducer are soldered to a small printed circuit board 190, mounted on an of connector 180. The of connector 180 is inserted into the open end 159 of the section 150 up to the lip 181 of the connector. mounted on the connector at a plastic ring 182 are three reed switches 184, 136 and 188. The reed I switches are wired to the printed circuit board 190. When the connector is inserted in the section 150 in the proper position, the reed switches are located under either side of the arc traversed by the magnet 164 as the ring 160 is turned. When the ring is turned to one detent position the magnet 164 is located over reed switches 184 and 186 to close them. And when the ring is in its other detent position the magnet is located over reed switch 188 to close it. The of connector 180 and copper shield 154 provide a completely shielded cavity for the wiring, printed circuit board, switches, and board components in the inside of the section 150.
Turning the ring performs three switching functions in the probe assembly. First, the focal characteristics of the transducer are switched between short focus using only the central disc of the transducer, and long focus by connecting the central disc and annular ring of the transducer together to be activated simultaneously.
Second, the tuning of the circuitry on circuit board 190 is switched to match the respective electrical characteristics of the transducer in the two operating modes. Third a resistance value on the circuit board is changed to produce a signal indicative of the operating mode, which signal is coupled out through the connector along with signals to and from the transducer.
Claims (14)
1. An ultrasonic transducer assembly for use with an ultrasonic diagnostic system, comprising piezoelectric material and exhibiting an effective radiating surface having a generally circular, concave shape with a center point, said effective radiating surface in cross-section resembling two symmetrical arctuate surfaces symmetrically disposed on either side of said center point and canted toward each other at an angle which is less than the angle traversed by a spherical surface of the same curvature as said arcuate surfaces and the same diameter as said effective radiating surface.
2. The ultrasonic transducer assembly of Claim 1, wherein said effective radiating surface is the surface of said piezoelectric material.
3. The ultrasonic transducer assembly of Claim 2, wherein said concave shaped piezoelectric material is electrically separated into a central concave member having an outer perimeter symmetrically disposed with respect to said center point, and an annular member symmetrically disposed about the perimeter of said central concave member.
4. The ultrasonic transducer assembly of Claim 1, wherein said effective radiating surface is formed by a conical disc of piezoelectric material having a concave face, and an acoustic lens located in front of said concave face and having a spherical face on the surface remote from said concave face.
5. The ultrasonic transducer assembly of Claim 4, wherein said acoustic lens comprises an epoxy material bonded to said concave face of said conical disc of piezoelectric material.
6. The ultrasonic transducer assembly of Claim 5, wherein said conical disc of piezoelectric material comprises a central conical disc and an outer annulus surrounding said central disc.
7. The ultrasonic transducer assembly of Claim 5, further comprising an annulus of backing material affixed to the back of said conical disc of piezoelectric material around the outer perimeter thereof.
8. The ultrasonic transducer assembly of Claim 1, wherein said piezoelectric material comprises a flat disc having a front face and including an acoustic lens mounted on said front face and having an aspheric surface remote from said flat disc of the shape of said effective radiating surface.
9. The ultrasonic transducer assembly of Claim 8, wherein said flat disc comprises a central disc and a separate annular ring disposed about said central disc.
10. An ultrasonic transducer assembly for use with an ultrasonic diagnostic system, comprising a conical surface of piezoelectric material, and an acoustic lens affixed to said conical surface and having a spherical surface remote from said conical surface.
11. The ultrasonic transducer assembly of Claim 10, wherein said acoustic lens comprises epoxy exhibiting a high acoustic impedance and velocity relative to human tissue.
12. The ultrasonic transducer assembly of Claim 10, wherein said conical surface of piezoelectric material comprises a central conical surface having an outer perimeter, and an annular surface disposed about said outer perimeter.
13. The ultrasonic transducer assembly of claim 12, wherein said central conical surface exhibits a first geometric focus and near field focus limit, and said central conical surface and annular surface together exhibit a second geometric focus and near field focus limit.
14. A dual aperture ultrasonic transducer assembly having a concave, symmetrical aspheric effective radiating surface, and including piezoelectric material separated into a central region and an annular region, said central region exhibiting a first geometric focus and a first near field focus limit, and said central region and annular region together exhibiting a second geometric focus and a second near field focus limit which are both more distant from said effective radiating surface than said first geometric focus and said first near field focus limit.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US40054782A | 1982-07-21 | 1982-07-21 | |
| US400,547 | 1982-07-21 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1212448A true CA1212448A (en) | 1986-10-07 |
Family
ID=23584041
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000432763A Expired CA1212448A (en) | 1982-07-21 | 1983-07-19 | Selectable focus sphericone transducer, imaging apparatus and switching means |
Country Status (1)
| Country | Link |
|---|---|
| CA (1) | CA1212448A (en) |
-
1983
- 1983-07-19 CA CA000432763A patent/CA1212448A/en not_active Expired
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