US20080015438A1 - High frequency, high frame-rate ultrasound imaging - Google Patents
High frequency, high frame-rate ultrasound imaging Download PDFInfo
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- US20080015438A1 US20080015438A1 US11/776,401 US77640107A US2008015438A1 US 20080015438 A1 US20080015438 A1 US 20080015438A1 US 77640107 A US77640107 A US 77640107A US 2008015438 A1 US2008015438 A1 US 2008015438A1
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- G—PHYSICS
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- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
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- A61B8/0833—Detecting organic movements or changes, e.g. tumours, cysts, swellings involving detecting or locating foreign bodies or organic structures
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- A61B8/4281—Details of probe positioning or probe attachment to the patient involving the acoustic interface between the transducer and the tissue characterised by sound-transmitting media or devices for coupling the transducer to the tissue
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- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
- G01S15/88—Sonar systems specially adapted for specific applications
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Abstract
A system for producing an ultrasound image comprises a scan head having a transducer capable of generating ultrasound energy at a frequency of at least 20 megahertz (MHz), and a processor for receiving ultrasound energy and for generating an ultrasound image at a frame rate of at least 15 frames per second (fps).
Description
- This application is a continuation of U.S. application Ser. No. 10/683,890, entitled “#HIGH FREQUENCY, HIGH FRAME-RATE ULTRASOUND IMAGING SYSTEM,” filed on Oct. 10, 2003, which priority to and the benefit of U.S. Provisional Application No. 60/417,164, entitled “#RMV SCANHEAD SYSTEM,” (attorney docket No. 14157PRO), filed on Oct. 10, 2002; U.S. Provisional Application No. 60/468,958, entitled “#SCAN HEAD FOR ULTRASOUND IMAGING SYSTEM,” (attorney docket No. T00518-0005-USP2 (190304-327786)), filed on May 9, 2003; U.S. Provisional Application No. 60/468,956, entitled “#REMOVABLE ACOUSTIC WINDOW,” (attorney docket No. T00518-0014-PROV-US (190304-326186)), filed on May 9, 2003; and U.S. Provisional Application No. 60/470,234, entitled “#METHOD AND APPARATUS FOR OBTAINING AN ULTRASOUND IMAGE,” (attorney docket No. T00518-0011-USP 1 (190304-325200)), filed on May 14, 2003, all of which are incorporated in this document by reference.
- Scanheads that were developed in the late 1970's and early 1980's for imaging human tissue are still useful for many ultrasound imaging applications. A transducer located in the scanhead comprises discs of piezoelectric material, which when excited electrically vibrated at a frequency usually chosen to be between 2 and 10 MHz. At these frequencies, the vibrational energy of the transducer was directional and radiated from two faces of a thin circular disc in reasonably well-defined beams. In general, the energy radiating from the back of the transducer is absorbed by a suitable material while that from the front is coupled to the patient by a fluid capable of transmitting ultrasound energy with low loss characteristics. Emerging through a thin, low-loss cap, the energy is further coupled to the patient with a sonolucent gel applied to the patient's skin. Echoes resulting from the interaction of the ultrasound energy with body tissue traverse the same path in reverse, and when they strike the transducer generate an electrical signal whose strength is a function of the echogenicity of a target within the patient and the target's depth below the patient's skin. The location in depth is determined from the time interval between the transmit pulse and the received echo. With this information and the directional information delivered by a position encoder coupled to the transducer, the scanheads generate a gray-scale image of the tissue lying in a scan plane within the patient, which is refreshed and updated with every sweep of the transducer across the image plane. Two sweeps of the transducer comprises one operating cycle, referred to as 1 Hz, and equates to two frames per second.
- Two dimensional ultrasound images (also known as B-scans) are made up of a number of adjacent lines of ultrasound data called A-scans, which are acquired from the scanhead through successive sweeps of the transducer. The line of ultrasound data is acquired when a transducer transmits the ultrasound pulse into the tissue being studied and then receives the ultrasound signal reflected by the tissue along a beam axis of the transducer. The lines of ultrasound data are located within the same plane and are usually spaced at constant intervals. Each line of data is acquired with the ultrasound beam axis moved laterally within the plane by a known incremental distance. The ultrasound image may have a linear format, in which the lines are parallel to one another and equally spaced, or a sector format, in which the lines radiate from an apex with equal angles between them. To produce a linear format image, the transducer is moved laterally, without altering the angle between the transducer and the line along which it is moved. To produce a sector format image, the transducer is mounted to a fixture, which rotates about an apex, causing the transducer to move in an arc. As the transducer moves, the position within the scan plane is tracked so that an associated ultrasound system can display the ultrasound line data at the correct locations within the displayed image.
- Early clinical diagnostic ultrasound systems used wobbler scanheads to produce the sector format images. These systems used low frequency ultrasound, in the 2 to 5 MHz range. The wobbler scanheads usually consisted of the transducer located within a fluid filled chamber, a motor, a position encoder, and an acoustic window through which the ultrasound passed. The motor drive mechanism usually moved the transducer through an arc, resulting in a sector scan type image format while the position encoder kept track of the transducer position. The wall of the fluid filled chamber, which faced the tissue being imaged, acted as an acoustic window, which was usually made of a hard plastic material. This window allowed ultrasound to pass through with little attenuation. Further, in general, there is a reflected ultrasound wave which does not pass through the window. This wave can reverberate between the transducer and the window several times before dissipating. The reverb components, which strike the transducer, can cause an undesirable artifact in the ultrasound image. The magnitude of the reflected wave is determined by the acoustic impedance mismatch between the material used for the window and the fluid in the transducer chamber. The amount of attenuation is determined by the window material, which occurs as the ultrasound energy passes through the window. Both attenuation and reflections at the window are undesirable.
- In the 80's these mechanically scanned transducers began to be replaced by solid state devices which consist of a plurality of narrow piezoelectric elements which, when excited sequentially, can be used to build up an image. These “#linear array” scanheads had been developed at the same time as the mechanical ones, but delivered poorer image quality. Further work, throughout the 80's and 90's resulted in the development of “#phased array” scanheads, which have the ability to excite groups of elements in ways that allows electronic beam steering and focusing, which in general produce better images than any mechanical scanhead and at frame rates of 60 frames per second. Today, phased arrays are universally used for ultrasound imaging of human tissue. However, a typical phased array system using a transducer operating at five MHz might have a spatial resolution of 0.5 mm.
- One disadvantage with higher operating frequencies is as the operating frequency increases, fabrication difficulties make it challenging to build a phased array type imaging system. As a result, current systems operating in the 30-40 MHz range typically use mechanically scanned single element transducers, in scanheads similar in operating principal to the mechanically scanned systems described above. However, high frequencies generally result in higher attenuation and thus the attenuation due to an acoustic window is increased significantly. Accordingly, current high frequency transducers use a non-encapsulated transducer, which is moved back and forth with a linear servo-motor and position encoder system. At higher frequencies (greater than 30 MHz), transducer encapsulation is impractical due to a breakdown of theoretical properties and characteristics of materials with higher frequencies.
- For high frequency transducers, since it is not encapsulated, the moving transducer is exposed. Acoustic coupling to the tissue being imaged is accomplished by creating a mound of ultrasound gel on the surface of the tissue, into which the moving transducer is lowered. Satisfactory imaging depends on the existence of a continuous layer of gel between the transducer and the tissue. If the transducer loses contact with the gel, or if an air bubble forms on the surface of the transducer, imaging will be compromised or even impossible. This type of imaging is restricted to relatively low frame rates, because a rapidly moving transducer will disrupt the gel layer and is more likely to lose contact. Further disadvantages of exposed transducers are that they can create a hazard to delicate tissue, and can also expose the transducer to possible damage from impact.
- A further disadvantage in mechanical ultrasound scanheads is the use of moving magnet motors. The attraction of the moving magnet type is that there is no need for flexible wires to deliver power to the drive coil because the drive coil is stationary and the permanent magnet is attached to the moving member or rotor. Furthermore, the magnet type motor is inefficient. The usual mechanical scanhead consumes up to three Watts of electrical power, which is converted into heat that must be dissipated through plastic walls of the scanhead housing. As the housing is generally a poor conductor of heat the internal temperature of the scanhead may rise, which in time can degrade materials, alter the acoustic properties of the device, and can even be uncomfortable to the subject. Another reason the magnet motor is inefficient is that in an effort to keep the oscillating mass low, the moving magnets are kept relatively small. To achieve a certain torque, motor currents are correspondingly high, which gives rise to a high Iˆ2R loss. These losses increase roughly as the square of the scanning rate.
- In one embodiment, the high-frequency, high frame-rate ultrasound imaging system comprises a scan head having a transducer capable of generating ultrasound energy at a frequency of at least 20 megahertz (MHz), and a processor for receiving ultrasound energy and for generating an ultrasound image at a frame rate of at least 15 frames per second (fps).
- Related methods of operation are also provided. Other systems, methods, features, and advantages of the high-frequency, high frame-rate ultrasound imaging system will be or become apparent to one with skill in the art upon examination of the following figures and detailed description. It is intended that all such additional systems, methods, features, and advantages be included within this description, be within the scope of the high-frequency, high frame-rate ultrasound imaging system, and be protected by the accompanying claims.
- The high-frequency, high frame-rate ultrasound imaging system can be better understood with reference to the following figures. The components within the figures are not necessarily to scale, emphasis instead being placed upon clearly illustrating the principles of the high-frequency, high frame-rate ultrasound imaging system. Moreover, in the figures, like reference numerals designate corresponding parts throughout the different views.
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FIG. 1A is a diagram of one embodiment of a scanhead system. -
FIG. 1B is a block diagram illustrating the ultrasound imaging system ofFIG. 1A . -
FIG. 2 is a perspective view of a scanhead of the system ofFIG. 1 . -
FIG. 3A is a side vide of the scanhead ofFIG. 2 . -
FIG. 3B is a top view of the scanhead ofFIG. 2 . -
FIG. 4 is section A-A view of the scanhead ofFIG. 3B . -
FIG. 5 is a detailed schematic view illustrating the scan head ofFIGS. 3A, 3B and 4. -
FIG. 6 provides further details of the scanhead ofFIG. 4 . -
FIG. 7 provides further details of the scanhead ofFIG. 3A . -
FIG. 8 demonstrates alternative motions of thepivot tube 6. -
FIG. 9 is a diagram of another embodiment of a scanhead of the system ofFIG. 1A . -
FIG. 10 is a longitudinal cross section of the scanhead ofFIG. 9 . -
FIG. 11 is a perspective view of an armature assembly in the scanhead ofFIG. 9 . -
FIG. 12 is a perspective view of a portion of the scanhead ofFIG. 9 . -
FIG. 13 is an exploded view of a release assembly of the scanhead ofFIG. 9 . -
FIG. 14 is an assembled view of the quick release assembly ofFIG. 13 . -
FIG. 15 is a perspective view of a seal of the scanhead ofFIG. 9 . -
FIG. 16 is a perspective view of the scanhead ofFIG. 9 in a testing configuration. -
FIG. 17A is a perspective view of a nosepiece for the scanhead ofFIG. 9 . -
FIG. 17B is a perspective view of the nosepiece ofFIG. 17 shown with an optional shroud. -
FIG. 18 is another view of the nosepiece ofFIG. 17 in a separated position. -
FIG. 19A is side view ofFIG. 17 . -
FIG. 19B is a detail view ofFIG. 19A . -
FIG. 20 is a cross section ofFIG. 17 . -
FIG. 21 is a cutaway ofFIG. 17 . -
FIG. 22 is an end view of nosepiece ofFIG. 17 . -
FIG. 23 is an end view of acoustic window ofFIG. 17 . -
FIG. 24 is a screen shot depicting an image on the display. -
FIG. 25 is a flow chart illustrating the operation of one aspect of the high-frequency, high frame-rate ultrasound imaging system. - Referring to
FIG. 1A , anultrasound scanning system 100 has anelectronics circuit 102 for transmitting and receiving a series ofultrasound pulses 104 to and from a probe orscanhead 106. Thescanhead 106 can b situated on a subject 108 to recordimage data 110 of ascan plane 112, representing a cross section of atarget 114 for display on adisplay 116. Thetarget 114 may be, for example, the organ of a small animal, such as a mouse, a rat or another research subject. Examples of organs that can be imaged include, but are not limited to, a lung, a heart, a brain, a kidney, a liver and blood flowing within the subject. Further, the ultrasound imaging system can be used to image a neo-plastic condition. Thecircuit 102 has a transmitsubsystem 118 for generating thepulses 104 and a receivesubsystem 120 for receiving thecorresponding echo pulses 104, which are directed to acomputer 122 for processing and eventual display as theimage scan data 110. Thescanhead 106 is coupled at 126 to thecircuit 102. Thescanhead 106 has atransducer assembly 124, with amembrane 125, which is coupled to aposition encoder 128 in conjunction with atorque motor 130. Theencoder 128 andmotor 130 monitor the position of thetransducer assembly 124 within thescanhead 106. Thecorresponding position data 132 is transmitted with thepulses 104, representing theimage data 110, to thecomputer 122. Thescanhead 106 can be used as an encapsulated real-time probe for recording and displayingimage data 110 obtained in real-time at high frequencies, such as but not limited to greater than 20 MHz and including 25 MHz, 30 MHz, 35 MHz, 40 MHz, 45 MHz, 50 MHz, 55 MHz, 60 MHz and higher. Further, transducer operating frequencies significantly greater than those mentioned above are also contemplated. - Referring again to
FIG. 1A , thesystem 100 also includes asystem processor 134. Theprocessor 134 is coupled to the display or monitor 116 and to a human-machine interface 136, such as a keyboard, mouse, or other suitable device. If themonitor 116 is touch sensitive, then themonitor 116 can be employed as the input element for the human-machine interface 136. A computerreadable storage medium 138 is coupled to theprocessor 134 for providing instructions to theprocessor 134 to instruct and/or configure the operation of themonitor 116 for recording and displaying thedata monitor 116. The computerreadable medium 138 can include hardware and/or software such as, by way of example only, magnetic disks, magnetic tape, optically readable medium such as CD ROM's, and semi-conductor memory such as PCMCIA cards. In each case, the medium 138 may take the form of a portable item such as a small disk, floppy diskette, cassette, or it may take the form of a relatively large or immobile item such as hard disk drive, solid state memory card, or RAM coupled to theprocessor 134. It should be noted that the above listedexample mediums 138 can be used either alone or in combination. -
FIG. 1B is a block diagram illustrating theultrasound imaging system 100 ofFIG. 1A . Thesystem 100 operates on a subject 114. Theultrasound probe 106 can be placed in proximity to the subject 114 to obtain image information. - The
ultrasound system 131 includes acontrol subsystem 127, ascan converter 129, the transmitsubsystem 118, the receivesubsystem 120 and theuser input device 136. Theprocessor 134 is coupled to thecontrol subsystem 127 and thedisplay 116 is coupled to theprocessor 134. Amemory 121 is coupled to theprocessor 134. Thememory 121 can be any type of computer memory, and is typically referred to as random access memory “#RAM,” in which thesoftware 123 of the high-frequency, high frame-rate ultrasound imaging system executes. - The high-frequency, high frame-rate ultrasound imaging system can be implemented using a combination of hardware and software. The hardware implementation of the high frequency, high frame-rate ultrasound imaging system can include any or a combination of the following technologies, which are all well known in the art: discrete electronic components, a discrete logic circuit(s) having logic gates for implementing logic functions upon data signals, an application specific integrated circuit having appropriate logic gates, a programmable gate array(s) (PGA), a field programmable gate array (FPGA), etc.
- The software for the high frequency, high frame-rate ultrasound imaging system comprises an ordered listing of executable instructions for implementing logical functions, and can be embodied in any computer-readable medium for use by or in connection with an instruction execution system, apparatus, or device, such as a computer-based system, processor-containing system, or other system that can fetch the instructions from the instruction execution system, apparatus, or device and execute the instructions.
- In the context of this document, a “#computer-readable medium” can be any means that can contain, store, communicate, propagate, or transport the program for use by or in connection with the instruction execution system, apparatus, or device. The computer readable medium can be, for example but not limited to, an electronic, magnetic, optical, electromagnetic, infrared, or semiconductor system, apparatus, device, or propagation medium. More specific examples (a non-exhaustive list) of the computer-readable medium would include the following: an electrical connection (electronic) having one or more wires, a portable computer diskette (magnetic), a random access memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or Flash memory) (magnetic), an optical fiber (optical), and a portable compact disc read-only memory (CDROM) (optical). Note that the computer-readable medium could even be paper or another suitable medium upon which the program is printed, as the program can be electronically captured, via for instance optical scanning of the paper or other medium, then compiled, interpreted or otherwise processed in a suitable manner if necessary, and then stored in a computer memory.
- The
memory 121 also includes the image data obtained by theultrasound system 100. A computerreadable storage medium 138 is coupled to the processor for providing instructions to the processor to instruct and/or configure processor to perform steps or algorithms related to the operation of theultrasound system 131, as further explained below. The computer readable medium can include hardware and/or software such as, by way of example only, magnetic disks, magnetic tape, optically readable medium such as CD ROM's, and semiconductor memory such as PCMCIA cards. In each case, the medium may take the form of a portable item such as a small disk, floppy diskette, cassette, or it may take the form of a relatively large or immobile item such as hard disk drive, solid state memory card, or RAM provided in the support system. It should be noted that the above listed example mediums can be used either alone or in combination. - The
ultrasound system 131 includes acontrol subsystem 127 to direct operation of various components of theultrasound system 131. Thecontrol subsystem 127 and related components may be provided as software for instructing a general purpose processor or as specialized electronics in a hardware implementation. Theultrasound system 131 includes ascan converter 129 for converting the electrical signals generated by the received ultrasound echoes to data that can be manipulated by theprocessor 134 and that can be rendered into an image on thedisplay 116. Thecontrol subsystem 127 is connected to a transmitsubsystem 118 to provide an ultrasound transmit signal to theultrasound probe 106. Theultrasound probe 106 in turn provides an ultrasound receive signal to a receivesubsystem 120. The receivesubsystem 120 also provides signals representative of the received signals to thescan converter 129. The receivesubsystem 120 is also connected to thecontrol subsystem 127. Thescan converter 32 is directed by thecontrol subsystem 127 to operate on the received data to render an image for display using theimage data 110. - The
ultrasound system 131 transmits and receives ultrasound data through theultrasound probe 106, provides an interface to a user to control the operational parameters of theimaging system 100, and processes data appropriate to formulate still and moving images that represent anatomy and/or physiology. Images are presented to the user through theinterface display 116. - The human-
machine interface 136 of theultrasound system 131 takes input from the user, and translates such input to control the operation of theultrasound probe 106. The human-machine interface 136 also presents processed images and data to the user through thedisplay 116. - Referring to
FIG. 2 , aframe 140 of thescanhead 106 consists of twoside plates position encoder 128 at a proximal end and to apivot frame 3 at a distal end. The position encoder 128 may be, for example, an optical encoder such as a Renishaw RGB25. Anosepiece 20 can be releasably attached to the distal end of thescanhead 106. Theside plates scanhead 106. In addition, the housing provides a strain relieved entry/exit point forcables 142 to and from thescanhead 106. The housing may include an RF shielding component. - Referring to
FIGS. 3A, 3B , 4 and 5 a pair ofball bearings 4 are positioned in thepivot frame 3 to locate arotor assembly 5, which allows thetransducer assembly 124 to pivot freely back and forth through an angle of approximately 20 degrees. Therotor assembly 5 comprises apivot tube 6 to which is connected ayoke 7. Screws through thepivot bearings 4 secure them to theyoke 7. Atransducer 8 of theassembly 124 is connected to the distal end of thepivot tube 6, and its'coaxial signal cable 8 a extends through thepivot tube 6 and out through aslot 6 a, and is affixed to acircuit board 23 of the circuit 102 (seeFIG. 1A ). At the proximal end of therotor assembly 5, a lightweight yetstiff paddle 9 supports arotor coil encoder code track 12 and aHall sensor magnet 13. A flexiblecoax cable 14 leads from therotor assembly 5 from the side opposite the transducer coax 8 a. Both of these are arranged to flex freely without binding or touching other structures as thetransducer assembly 124 oscillates back and forth within thescanhead 106. Overall is fitted aplastic housing mount nut 32 is secured between the twohousing halves mount nut 32 has a threaded hole by which thescanhead 106 can be attached to a support arm (not shown), if desired. - Further referring to
FIGS. 3A, 3B and 4, thenosepiece 20 is filled with anacoustic coupling fluid 15. The distal end of thescanhead 106 is sealed by theacoustic window 125, which comprises acoustically transparent plastic film and which will be described in further detail below. An o-ring 17 creates a seal between thenosepiece 20 and thenose 18 of thepivot frame 3. Arubber seal diaphragm 19 is located between thenose 18 and thepivot frame 3 making a fluid tight seal. Another fluid tight seal is created between the seal diaphragm and thepivot tube 6 because a hole for thepivot tube 6 in theseal diaphragm 19 is smaller than the pivot tube, creating a tight seal when theseal diaphragm 19 is placed over thepivot tube 6 during assembly. During operation, theseal diaphragm 19 flexes to allow thepivot tube 6 to oscillate back and forth while maintaining the fluid seal there-between. To reduce the degree of flexing of theseal diaphragm 19, it contacts thepivot tube 6 approximately at its pivot point. Theyoke 7 straddles this point to clear theseal diaphragm 19. A lockingplate 34, comprising, for example, a bayonet-type locking mechanism is located on the back of thenosepiece 20. When thenosepiece 20 is placed over thenose 18, the heads of twoscrews 34 a pass through holes in the lockingplate 34. A twist of approximately 10 degrees in one direction causes the shank ofscrews 34 a to travel in short curved slots in the lockingplate 34, trapping the heads ofscrews 34 a as shown and locking thenosepiece 20 to thescanhead pivot frame 3. It is noted that thenosepiece 20 can be removed by simply reversing this action. Afill port 35 can be used to initially fill ahollow cavity 15 innosepiece 20 with acoustic fluid, and to periodically access thecavity 15 to remove any bubbles that may appear. - Referring again to
FIGS. 3A, 3B and 4, thetransducer assembly 124 is attached to the distal end of thepivot tube 6, creating a fluid tight seal. When in motion, the distal face of thetransducer 8 remains a fixed distance (such as, but not limited to, between 0.5 mm to 1 mm) from theacoustic window 125. The coaxialelectrical cable 8 a, carrying signals to and from thetransducer 8, leads down the center of thepivot tube 6 and emerges through theslot 6 a near the pivot axis, thus minimizing motion of thecoax cable 8 a. A slack length ofcoax cable 8 a absorbs relative motion during operation, situated between theslot 6 a and its termination point at the proximal end, i.e. the small printed wiring board (PWB) 23. To this end, thecoax cable 8 a and thecoax cable 14 are constructed to have a long flex life. For example, thecables PWB 23 contains a pre-amplifier for signals coming from thetransducer 8, and acts as a termination point for the signal, power and ground wires from the twoHall sensors 13. ThePWB 23 also receiveswires 21 entering thescanhead 106 through acable cap 33 and anencoder cable 25 a. - Referring to
FIGS. 3A, 3B , and 4rotor windings FIG. 6 asnumeral 10, anencoder code track 12 and the Hallsensor actuating magnets 13 are all bonded to the proximal end of thepivot tube 6. Anintermediate support structure 27 can be made of rigid polyethylene foam sandwiched between, for example, thin (0.1 mm) epoxy-glass board, forming a lightweight but rigid core to support therotor windings 24 and theencoder code track 12, in particular. - Referring to
FIG. 3B andFIG. 4 , thebacking iron plates side plates Field magnets backing iron plates field magnets magnet rotor assembly 5 moves back and forth in the gap between the twomagnets magnet 28 faces the north pole across the gap ofmagnet 28 a. The north pole ofmagnet 28 faces the south pole ofmagnet 28 a. There are two pole gaps between the facingmagnets portion 10 a of therotor coil 10 is constrained to oscillate within the confines of one pole gap, and anotherportion 10 b oscillates in the other gap. - Referring to
FIG. 5 , an exploded view of thescanhead 106 including therotor assembly 5, is shown. - Referring to
FIG. 6 , thetorque motor 130 rotates the tube orsupport arm 6 on the pivot back and forth through a limited angle, i.e. approximately 10-14 degrees. Thetransducer assembly 124 is connected to one end of thesupport arm 6, and the positionencoder code track 12 is connected to the other end. Thetransducer 8 of theassembly 124 is aimed such that a focused ultrasound beam can be directed along the longitudinal axis of thepivot tube 6, away from the pivot point. The case andnosepiece 20 surround thetorque motor 130,position encoder 128 andtransducer 8 such that thetransducer 8 is located within thenosepiece section 20. Thenosepiece section 20 can be filled with water (or another medium suitable for conducting ultrasound); thetorque motor 130 andposition encoder 128 are dry due to theseal 19. Thepivot tube 6 passes through theflexible seal 19, enabling thepivot tube 6 to move back and forth. Theacoustic window 125 can be located at the end of thenosepiece 20. - The position encoder 128 used in the
scanhead 106 is, for example, an optical encoder capable of 1 micron (μm) resolution. The position encoder 128 works in conjunction with a reticulated tape strip referred to herein as theencoder code track 12. Theposition encoder 128 makes use of an optical sensor to count the passage of reticules on theencoder code track 12 as they pass a sensor associated with theposition encoder 128. The sensor can sense both direction of travel of theproximal end 150 of thepivot tube 6, and track the position of the travel of thedistal end 152 of thepivot tube 6 to within 1 micron. - Referring again to
FIG. 6 , theencoder code track 12 can be connected to the rear of thepivot tube 6 of thescanhead 106 at a known radial distance from thepivot point 154 of thepivot tube 6. Theencoder code track 12 is attached to a precise surface having a radius such that theencoder code track 12 is everywhere tangential to a chord traced out by thepivot tube 6. As thepivot tube 6 pivots, theencoder code track 12 passes back and forth under the optical sensor in theposition encoder 128. The result is the digitization of the position of thedistal end 152 of thepivot tube 6 at the radius at which theencoder code track 12 is fixed. The position information can be used to determine the location of thetransducer 8 located the same radial distance from the pivot point on the other end of thepivot tube 6. Dissimilar distances of theproximal end 150 anddistal end 152 measured from thepivot point 154 can also be used, if desired. The optical coupling between theposition encoder 128 and theproximal end 150 of thepivot tube 6 reduces the transmission of electronic noise generated by theposition encoder 128 and thecircuit 102 from thetransducer 8. - The
transducer 8 can be a high-frequency single-element focused piezoelectric ultrasonic transducer, with a frequency greater than 30 MHz and can be around 40 MHz. Thetransducer 8 receives the RFelectrical pulse 104 as input and produces an ultrasonicacoustic pulse 104 as output during the transmit phase of operation of the circuit 102 (seeFIG. 1A andFIG. 1B ). The reverse process is performed during the receive phase such that the input to thetransducer 8 is an ultrasonicacoustic pulse 104 which is converted by thetransducer 8 into a radio frequency electrical signal, represented bydata 110. Thetransducer 8 used in thescanhead 106 can be abroadband transducer 8 fabricated in such a way to ensure a good acoustic match to the acoustic medium in thecavity 15. - The
pivot tube 6 can be an ultra light weight stainless steel tube fixed by the bearingassembly 4 in such a way that it pivots about itsmidpoint 154. Thetransducer 8 is connected to one end of thepivot tube 6, while theencoder code track 12 is connected to the other end of thepivot tube 6. Thepivot tube 6 houses the coils of thetorque motor 130 between the bearingassembly 4 and theencoder code track 12, thus forming an integral part of thetorque motor 130. Made of tubing, thepivot tube 6 also acts as a conduit for the transducer coaxcable 8 a. - Referring to
FIG. 7 , thepivot axis bearing 4 comprises a pair of ball bearings and an off axis, or offset,clamp 146, which holds thepivot tube 6. The offsetclamp 146 allows the pivot point of thepivot tube 6 to remain accessible for the routing ofcables 8 a and mechanical attachment to and from thepivot tube 6. Thebearing 4 can be fabricated with precise bearings and accurately machined components to ensure highly repeatable one axis rotation about thepivot point 154. The offsetclamp 146 is connected to thepivot tube 6 at one end and is rotatably attached to thepivot point 154 at the other end through pins 148. - The
flexible seal 19 can be attached to the midpoint of thepivot tube 6, and the rear of thenose piece 20 bayonet quick release assembly comprising the lockingplate 34 and the twoscrews 34 a. Theseal 19 can be made of an elastomer membrane that is fastened so that it forms a fluid tight seal between thepivot tube 6 and thenosepiece 20. Theseal 19 separates the fluid fillednosepiece 20 from the remainder of the housing which remains dry. - Two
Hall sensors 13 are placed in the housing of thescanhead 106 so that they sense the travel of thepivot tube 6 past theirrespective sensors 13. Thesensors 13 are placed so that they produce a signal at the maximum safe travel of thetorque motor 130. The limit switches 13 are also placed symmetrically about thepivot point 154 so that they can be used to home the system to a zero deflection, homed, or normal position. - The
hollow cavity 15 in thenose piece 20 can be fluid filled. Thenosepiece 20 provides a mounting structure to which theacoustic window 125 can be attached. Thenosepiece 20 features a drain/fill screw as afill port 35 through which fluid may be added or removed from thecavity 15. Thenosepiece 20 can contain part of a bayonet style quick release assembly allowing it to be removed and changed quickly without the need for tools, while ensuring a fluid tight seal. - The
acoustic window 125 comprises a thin membrane of a material well acoustically matched to the fluid in thecavity 15. Theacoustic window 125 can be held in a position so that it remains close to and normal to the face of thetransducer 8 over the full extent of transducer travel (approximately 0.5 mm to 1 mm, for example). Material from which to form the acoustic window were initially selected or rejected based on known bulk acoustic properties. The membrane can be chosen to exhibit acoustic impedance in the range of 1.3 to 1.7 megaRayles (MRayles), such as 1.5 megarayles. Mechanical constraints such as the manner in which the membrane is attached affect the acoustic impedance and the resulting suitability for use as theacoustic window 125. Material from which the acoustic window can be fabricated include polyester films ranging in thickness from about 0.9 um to 4.5 μm, polytetrafluoroethylene (PTFE) in thicknesses of 5 μm, 10 μm, 15 μm, and 25 μm, low density polyethylene (LDPE) in thicknesses of 15 μm, 25 μm, and 50 μm, polycarbonate in a thickness of 2 μm, polypropylene in a thickness of 4 μm, latex elastomer in a thickness of 60 μm, and silicone elastomer in a thickness of 25 μm were tested in a variety of configurations including varying the angle of incidence of the ultrasound beam to the membrane forming theacoustic window 125 from 90 degrees to 110 degrees. These materials and thicknesses were used with transducer frequencies of 30-40 MHz. Thinner membranes could be used as the frequency increases. In addition, the encapsulated coupling fluid can be varied to improve the acoustic match with the membrane of theacoustic window 125. For example, ethylene glycol, triethylene glycol, water, light paraffin oil and various aqueous solutions of glycols can be used. Water as a coupling fluid and a 25 μm thick membrane of LDPE can be used as the membrane for theacoustic window 125. Further, anacoustic window 125 formed of 5 μm thick or 15 μm thick PTFE are provided. In addition, thin silicone elastomer can also be provided for the membrane forming theacoustic window 125. Theacoustic window 125 maintains a fluid tight seal between thenosepiece 20 and the outer environment of thescanhead 106. Accordingly, theacoustic window 125 used with a highfrequency ultrasound transducer 8 is thin, and can be composed of a material that has an acoustic impedance very close to that of the fluid in thecavity 15. - The
electronics circuit 102 provides both a low noise RF preamplifier and a proprietary high fidelity protection circuit to thescanhead 106. Theelectronics circuit 102 protects sensitive receive instruments in the receivesubsystem 120 from thehigh energy pulse 104 used to drive thetransducer 8. The low-noise preamplifier boosts the signal of thetransducer 8 with minimal distortion. - Referring again to
FIGS. 3A, 3B and 4 during operation of thescanhead 106, when a direct current (DC) voltage signal is applied through therotor coil 10 through thecoax cable 14, the Lorentz forces generated by the currents inrotor coil portion 10 a androtor coil portion 10 b act in the same sense, causing therotor assembly 5 to rotate either clockwise or anti-clockwise about thepivot bearings 4, depending on the polarity of the applied voltage. When thescanhead 106 is started, a DC voltage signal is applied to therotor coil 10 to drive therotor assembly 5 towards one end of its range of motion. Before therotor assembly 5 reaches the end of travel, theHall sensor 13 triggers one of twoHall sensor magnets side plates control subsystem 127 responds by reversing the polarity of the voltage supplied to the rotor, driving therotor assembly 5 in the opposite direction until theother Hall sensor 13 is triggered. All this time, theposition encoder 128 reads theencoder code track 12 and determines the position of thetransducer 8 relative to the two end-of-travel events indicated by theHall sensors 13. The control system can now drive thetransducer 8 back and forth over whatever path and velocity profile is programmed into the controller, using the signals from theposition encoder 128 for positional feedback. - For example, M-mode and Doppler are two other modes of operation for which the
scanhead 106 is suited. For either of these modes, therotor assembly 5 is electrically driven to a fixed position, usually under operator control using a joystick associated with the human-machine interface 136 for input commands. The operator (not shown) can view an image frozen in time on thedisplay 116, or a series of images, which are periodically updated, and manipulate the direction in which thetransducer 8 is pointing. An electronic representation 144 (FIG. 1A ) of the direction in which thetransducer 8 is pointing can be displayed over the ultrasound image on thedisplay 116, and can be used for visual feedback. For the diagnostic imaging of tissue, the propagation path of ultrasound should be entirely within water or another fluid which has acoustic impedance very close to that of tissue. An air gap, or a material located in the path which creates an acoustic impedance mismatch can cause unwanted reflections, which appear as artifacts in the image on thedisplay 116. Usually a coupling gel, which has acoustic properties very similar to water, can be used between thescanhead 106 and the tissue being imaged. - Further, the
torque motor 130 in conjunction with theposition encoder 29 andencoder code track 12 run in a closed loop. They act as a servo-motor and are controlled by a motor control system associated with theprocessor 134 so that thepivot tube 6, which can be fixed in place by thepivot bearings 4, rotates back and forth about thepivot axis 154 in a controlled manner. Thetransducer 8 can be fixed to the end of thepivot tube 6 opposite theencoder code track 12. Thepivot tube 6 moves thetransducer 8, which is scanned back and forth within the fluid fillednosepiece 20. The location of thetransducer 8 is known at all times to within 1 micron. Thetransducer 8 transmits and receives ultrasonic information which is received and amplified via thecircuit 102, and then sent to theprocessor 134. Due to the light-weight precision nature of the design, this process can be accomplished at 15 Hz allowing for the production of real-time images for display of theimage data 110 on thedisplay 116. Operating thetransducer 8 at a frequency of 15 Hz equates to a frame rate of 30 frames per second, as two sweeps of thetransducer 8 through its range of motion equates to one Hz. Further, the oscillating frequency of thetransducer 8 may be increased to increase the frame rate. Further, depending on the frequency of the ultrasound energy transmitted by the transducer, theultrasound system 131 provides images having a spatial resolution of less than 30 microns. For example, at a frequency of approximately 25 MHz, the spatial resolution is approximately 75-100 microns. As the transducer frequency increases, the spatial resolution improves. At high transducer frequencies in the range of 40 MHz to 60 MHz, spatial resolution may exceed 30 microns. The high operating frequency of the transducer and the precise mechanical positioning of the transducer with an accuracy of approximately 1 μm allow theultrasound system 131 to provide real-time ultrasound images having spatial resolution in excess of 30 μm. - Further, the
scanhead 106 can be designed for use either by hand or on a fixture. Thescanhead 106 can also be used as an immersion style scanner in a water bath or it can be coupled with gel to the tissue to be scanned. In these situations, the membrane of theacoustic window 125 may be removed. - In summary, the
scanhead 106 is an electrically driven handheld imaging device that oscillates theultrasound transducer 8 in a fan-shaped arc while maintaining good acoustic coupling between thetransducer 8 and the subject 108 being imaged. Theposition encoder 128 delivers real-time position information to the controllingsystem processor 134. As thetransducer 8 moves, signals from theposition encoder 128 trigger transmitpulses 104 and communicate to thesystem processor 134 the position at which the resultingdata stream 110 collected between thosepulses 104 should be displayed in the electronic image that comprises the visual output on thedisplay 116. Thescanhead 106 can move thetransducer 8 continuously back and forth within a fluid environment over a distance of approximately 10 mm in a controlled manner at a rate up to and exceeding 15 Hz, which corresponds to a frame rate of 30 frames per second. The position encoder 128 in thescanhead 106 can record the position of thetransducer 8 in real time with an accuracy of 1 μm, and can position thetransducer 8 at an arbitrary location within the scan region to an accuracy of 1 μm. Thescanhead 106 includes theacoustic window 125 through which the ultrasound energy can be directed towards the subject 108 being imaged. Theacoustic window 125 allows the transmission of high frequency ultrasound with minimum attenuation and/or reflection. Thescanhead 106 can be sufficiently compact to be easily hand held, and can achieve positioning accuracy to 1 μm with a 15 Hz mechanical pivoting scanning and positioning system. Theacoustic window 125 can be compatible with the transmission of high frequency ultrasound energy, at frequencies in excess of 60 MHz. Thescanhead 106 can have image resolution smaller than 30 μm, with an imaged region of approximately 8 mm by 8 mm for the scan plane 112 (seeFIG. 1A ). - The
scanhead 106 uses a single moving part, thepivot tube 6, and a limitedangle torque motor 130 of the moving coil type. Thetorque motor 130 produces large torque force with little current draw because thenon-moving field magnets rotor windings 24. Another benefit of using a moving coil type motor is that the rotor mass, and rotational inertia, can be minimized, which helps to reduce power consumption and vibration. Small structures within the subject 108 being imaged at 40 MHz or greater are often associated with rapid movement. Therefore, such a design allows for operating speeds of 30 Hz or higher, corresponding to 60 frames per second. - The flex seal 19 (see
FIG. 4 ) isolates the fluid in thecavity 15 from the elements on the opposite side of theflex seal 19. Theflex seal 19 can be located near thepivot point 154 of therotor assembly 5 by using the offsetclamp 146 to allow thepivot bearings 4 to straddle the point where theflex seal 19 can be attached to thepivot tube 6, which helps to minimize the stresses on theflex seal 19. The attachment of theflex seal 19 can be accomplished by a simple friction fit between the hole in theflex seal 19 and thepivot tube 6. Theflex seal 19 can be made of a polyurethane elastomer possessing high fatigue life. - The portion of the
pivot tube 6 immersed in the acoustic fluid, and thetransducer 8, which can be wholly immersed, can be designed to be neutrally buoyant. When in motion, neutral buoyancy helps cancel vibration that could otherwise be a consequence of the motion of thetransducer 8 andpivot tube 6. In fact, in another embodiment of the present invention, the entire oscillating mechanism on either side of thepivot point 154 can be so adjusted to be neutrally buoyant and operates entirely immersed in the acoustic fluid. This can help to eliminate virtually all vibration that would otherwise be transmitted to the operator and the subject 108. - Further, the
nosepiece 20 can be easily removed and replaced by the operator. The simplified removal and replacement of thenosepiece 20 facilitates the replacement of a damagedacoustic window 125 or contaminated acoustic fluid. The fill port can be provided on the side of thenosepiece 20 to initially fill thecavity 15 with acoustic fluid when thenosepiece 20 is installed and to displace any bubbles with additional fluid should they develop with use. A simple bayonet type twist lock can be used to secure thenosepiece 20 to the body of thescanhead 106. If thenosepiece 20 should be sterile, as it might for some uses, it can be disposable. An integral part of such areplaceable nosepiece 20 can be a sterile drape or sheath, made of thin plastic, heat sealed or otherwise attached to the base of thenosepiece 20, which could be an injection molded plastic part. Thescanhead 106 can also be operated, if desired, with theacoustic window 125 removed. - Referring to
FIG. 8 , thescanhead 106 can be designed for reciprocal motion of thearm 6 with anappropriate flex seal 19, if desired. Theflex seal 19 could be of an accordion design, if desired. - Another embodiment of the
scanhead 106 is shown inFIGS. 9 and 10 . This embodiment of the scanhead, referred to usingreference numeral 206, has many components similar in function to components in the previous embodiment, which will be understood from the previous description. Thescanhead 206 includes achassis 215 capable of supporting all of the components of thescanhead 206. Acircuit board 224 is integrated into thescan head 206. Thechassis 215 supports a strainrelief clamp base 225 a, astrain relief clamp 225 b and astrain relief 226 a for securely holding acable assembly 226 b at a proximal end of thechassis 215. Thecable assembly 226 b connects toelectrical connectors circuit board 224. Thecircuit board 224 includes a motor control element, position monitoring circuit and communicates RF signals between the transducer and the processing elements in the ultrasound system 131 (seeFIG. 1B ). - The
chassis 215 supports apivot frame 208 that in turn supports ayolk 212 attached to armature 240 (FIG. 11 ) at a distal end of thechassis 215. Thearmature 240 is described in further detail below with reference toFIG. 11 . - A bayonet
style lock plate 205 a interfaces with a fixture on anose 205 that is mounted to thepivot frame 208. Thelock plate 205 a is attached to aremovable nosepiece 201 a. Thenosepiece 201 a has an acoustic window including amembrane 201 b mounted at one end thereof. Thenosepiece 201 a surrounds acoupling fluid cavity 201 c. The assembly comprising thenosepiece 201 a andlock plate 205 a is mounted onto thescan head 206 via the bayonet style lock system. - The
coupling fluid cavity 201 c surrounds atransducer 202 a, which is attached to thesupport arm 203. Thetransducer 202 a is connected to a transducercoaxial cable 202 b, which is connected at the opposite end to thecircuit board 224. Thenosepiece 201 a includes a fill port to fill thecoupling fluid cavity 201 c with a coupling fluid. The fill port is sealed by afill port screw 204. A moldedrubber seal 207 is mounted on thesupport arm 203 and disposed between thefluid cavity 201 c and apivot frame 208. - A bearing assembly including a
bearing preload screw 209, precisionradial ball bearings 208 a, and a fixingscrew 210 a affixes thearmature assembly 240, to thepivot frame 208, with low radial drag and virtually no radial or axial play. Ayoke 212 is provided straddling thesupport arm 203 and fixed to therotor 218 with rotor adhesive pins 214. - A partial assembly 250 of the
scan head 206 shown inFIG. 12 includes arear backing iron 216 a, a pair of backing iron posts 227 a and 227 b,rear field magnet 217 a. Amagnet wire coil 218 b wound around therotor 218 to form the armature of the torque motor. An opticalencoder code track 219 is attached to one end of therotor 218 such that it is at all points tangent to the motion of the torque motor. An optical encoder readhead 220 is affixed to an encoder adjustment slide 223 a as shown inFIG. 12 . The encoder adjustment slide 223 a is fitted to thechassis 215 so that it can slide allowing adjustment of theoptical read head 220 with respect to theencoder code track 219, which is fixed to thearmature 240. The movement is precise and controlled, and when the encoder readhead 220 is in the optimal position such that maximum signal strength is obtained at the encoder readhead 220, the readhead adjustment slide 223 a is locked in place with read head locking screws 223 c. Because the optical encoder is focused, it can be positioned at a known distance from the reflectiveencoder code track 219. This distance corresponds to a maximum encoder signal. Ahelical spring 223 d coupled to the readhead adjustment screw 223 b helps prevent backlash. Theoptical read head 220 combined with theencoder code track 219 allows the position of thearmature 240 to be recorded with an accuracy of 1 μm. A pair ofoptical limit switches 221 a are provided on thecircuit board 224 for determining the absolute position of thearmature 240 with respect to thechassis 215, and to protect against over travel of thearmature 240. Areflective surface 221 b attached to therotor 218 reflects signals from theoptical limit switch 221 a. - As shown in
FIGS. 9 and 10 , thechassis 215 includes a quick release hard mount jack 222 a. This mechanism is part of a quick release assembly, which is described in greater detail below with reference toFIGS. 13 and 14 . - A case comprising a
case top 233, acase bottom 234 and a case gasket 228 provides a fluid-tight seal around the internal components of thescan head 206. Thecase top 233 and case bottom 234 as well as the case gasket 228 are coated with an electrically conductive coating 251 to improve RF shielding. - Referring to
FIG. 11 , thearmature 240, thesupport arm 203, the transducer, 202 a, and the moldedseal 207, are shown in more detail. Thearmature 240 can be fabricated from precision machined components, which facilitates manufacturability, reduces cost, and improves performance compared to the composite construction used in the embodiment referred to above. Thesupport arm 203 is removable and can be mounted via thesupport arm mount 213 and twoshoulder bolts yoke 212 and therotor 218. It will be recognized therefore that a damagedtransducer 202 a and/or moldedseal 207 may be replaced without replacing theentire armature 240. - The
encoder code track 219 is made from a spring steel substrate. Theencoder code track 219 can be installed using a technique which avoids prebending of theencoder code track 219. Prebending may damage theencoder code track 219. Two encodercode track retainers 230 a hold theencoder code track 219 at each end, forcing the spring steel to take the exact curvature of therotor 218. Theencoder track retainers 230 a are fixed inplace using screws 230 b. Alternatively, a light string may be tied aroundscrews 230 b and adhered, using, for example, a glue, to the ends of theencoder code track 219 - The
scanhead 206 of this embodiment provides a sweep angle greater than 22 degrees included. The sweep angle refers to the motion of thetransducer 202 a defined by theHall sensor 13, the twoHall sensor magnets limit switches 221 a. In addition to the increased sweep angle due to theremovable support arm 203, the length of thesupport arm 203 may be changed, during manufacture or after, such as during field service, to accommodate different imaging requirements. Thesupport arm 203 can be a length such that thetransducer 202 a is approximately 20 percent farther from thepivot point 154 than the encoder code track 219 (seeFIG. 9 ). This configuration provides a scan width of over 15 mm measured at thetransducer 202 a. - The
scan head 206 in this embodiment is assembled on therigid chassis 215. Thescan head 206 can be assembled to complete functionality on thechassis 215 so that testing can be performed without thecase chassis 215 therefore allows verification of wire routing and strain relief, electrical inspection, tuning of the optical encoder readhead 220, and function verification of thelimit switches 221 a. - Referring to
FIGS. 13 and 14 , the quick release hard mount is shown in more detail. The quick release mechanism uses a spring loaded bayonet lock to quickly mount and remove thescanhead 206. The quick release hard mount plug 222 b includes a locatingpin 222 c at the end proximal to the quick release hard mount jack 222 a. The hard mount plug 222 b includes a quick releaseupper feature 222 d adjacent to the locatingpin 222 c, and ahelical spring 222 f adjacent to the locatingpin 222 c. The locatingpin 222 c allows thescanhead 106 to be mounted and remounted in precise 90 degree increments. A retainingring 222 e bears against the hard mount plug 222 b when attached to the hard mount jack 222 a as seen inFIG. 14 . - Referring to
FIG. 15 , thenose 205 is shown in more detail. Thenose 205 includesgasket bosses 206 b, which prevent damage to the molded seal 207 (FIG. 11 ) when clamping the moldedseal 207 between thenose 205 and thepivot frame 208. Theseal 207 can be made from a soft, flexible elastomer. The molded shape provides a centered rest position and eliminates stretch mode deformation of theseal 207 during operation. By contrast, a flat seal undergoes both bending and stretching during operation, resulting in two distinct loads on the motor, which can be difficult to compensate for. The moldedseal 207 can be designed like a shifter boot on an automobile's gear shift. It undergoes only bending deformation, which results in a lower and more uniform load on the motor. - The
scanhead 206 includes anintegral circuit board 224 that integrates motor control functions, position monitoring functions, and the transmission and reception of RF signals. In addition, thecircuit board 224 houses theoptical limit switches 221 a. Thecircuit board 224 can be prefabricated and tested. Thecircuit board 224 allows the routing of the transducercoaxial cable 202 b and themotor wires 232 to be made with a minimal drag on the motor by placing the connection points nearly over the pivot point. - The
case scanhead 206. It serves to waterproof and keep the internal components of thescanhead 206 free of contamination. Thecase chassis 215 by screws. Alternatively, the twohalves scanhead 206 tamper and water resistant. - The
nosepiece 201 a may include a disposable acoustic window. Referring toFIGS. 17A, 17B , 18, 19A, 19B and 20-23, the structure of thenosepiece 320 andacoustic window 330 are shown. Theacoustic window 330 is similar to theacoustic window 125 described above. Thenosepiece 320 includes afill port 322 for receiving fluid. Thenosepiece 320 has ashoulder 324 at the end proximal to theacoustic window 330 when attached. Arecess 326 and alip 328 are located adjacent theshoulder 324 for forming a snap fit with theacoustic window 330. -
FIG. 17B shows thenosepiece 320 with anoptional shroud 340 attached. Theshroud 340 attaches to theacoustic window 330 to protect thenosepiece 320 and scanhead 206 from contamination by liquid or biological material. - As shown in
FIG. 21 , theacoustic window 330 includes agroove 332 with a shape complementary to thelip 328 in thenosepiece 320. - The
acoustic window 330 can be designed to overcome the specific challenges of encapsulating a high frequency high-resolution ultrasonic probe in a variety of demanding environments. Theacoustic window 330 provides an inexpensive means for protecting the transducer and allowing imaging in a sterile environment without unduly compromising acoustic performance. Theacoustic window 330 can be constructed from a molded plastic frame comprising a fluid tight mechanical snap-on attachment structure. Theacoustic window 330 can be a molded, disposable element, which ‘snaps’ onto a permanent machined nosepiece, yielding the fluid filled encapsulated nose of the probe. Tools are not required to remove or attach the acoustic window to the nosepiece. For example, the shape of the acoustic window permits attachment to the nosepiece of the transducer using a simple rolling motion. The acoustic window can be any shape depending upon the nosepiece to be covered. A thin film of a sonolucent material forms amembrane 352 that can be attached to the front face of aframe 350. Theframe 350 and themembrane 352 comprise theacoustic window 330. - The characteristics and thickness of the material forming the membrane of the acoustic window are chosen to suit the characteristics of the specific probe to be encapsulated. Sonolucent materials, for example those disclosed in U.S. Pat. Nos. 5,479,927; 5,983,123; and 6,574,499, which are incorporated by reference in their entireties, can be used to produce the
membrane 352 of theacoustic window 330. In one aspect, the sonolucent material can be a polyester, a polycarbonate, an acrylic, a thermoplastic elastomer, or a silicone elastomer. Examples of sonolucent materials include, but are not limited to, Surlyn® ionomers, such as Surlyn® 8940, and Kapton®, available from E.I. Du Pont de Nemours and Company, Wilmington, Del.; polymethyl pentenes, such as TPX® MX-002, TPX® 95 and MX-004, available from Mitsui & Co., Tokyo, Japan; Teflon®, Mylar®, polyethylene, such as low density polyethylene, polycarbonate, polypropylene, and various polyurethane films. In one embodiment, the sonolucent material can be extruded to a certain thickness and heat welded to theframe 350 of theacoustic window 330 to form a fluid tight seal. The thickness of themembrane 352 will vary depending upon the sonolucent material selected. In one aspect, themembrane 352 has a thickness of less than or equal to 25 μm. In another embodiment, the thickness of themembrane 352 can range from 1 μm to 25 μm. The technology used for sealing themembrane 352 to theframe 350 will vary depending on the sonolucent material selected. Examples of methods for sealing themembrane 352 to theframe 350 include, but are not limited to, adhesives, welding techniques (e.g., RF, ultrasonic, and thermal), and mechanical seals. - Referring to
FIGS. 20 and 21 , the snap structure comprises agroove 332 in theframe 350. Thenosepiece 320 to which theacoustic window 330 will attach incorporates alip 328. Thelip 328 can be slightly oversized negative with respect to thegroove 332 in theframe 330. Theacoustic window 330 can be pressed onto thenosepiece 320 so that a positive fit is obtained when fully in place due to the seal formed between thelip 328 and thegroove 332. This fit is also fluid tight due to the interference type fit of thegroove 332 andlip 328. Before fitting theacoustic window 330 onto thenosepiece 320, the nosepiece can be partially filled with a coupling fluid. Examples of coupling fluid include, but are not limited to, water, ethylene glycol, triethylene glycol, light paraffin oil and various aqueous solutions of glycols. After fitting theacoustic window 330, air bubbles can be removed and the nosepiece/acoustic window assembly fully filled with coupling fluid via thefill port 322 located on the side of thenosepiece 320. - For environments requiring complete isolation of the probe from the surroundings, a sheathed version of the
acoustic window 330 includes a heat sealedsheath 340 of polyethylene film that can be designed to fit back over the probe and up the cable. The sheath can be formed as part of the disposableacoustic window 330, so that when sterilization is desired the entire window and sheath can be removed and discarded. - In an alternative embodiment, the high-frequency, high frame-rate ultrasound imaging system may be used to image a syringe, catheter, or other invasive element inserted into a subject.
FIG. 24 is a screen shot depicting animage 360 on thedisplay 116. The image includes anembryo 368. Theembryo 368 includes ahead 366 and auterus 362. Theultrasound system 131 can be used to visualize and guide theneedle 364 as it enters theuterus 362 of theembryo 368. -
FIG. 25 is aflow chart 400 illustrating the operation of one aspect of the high-frequency, high frame-rate ultrasound imaging system. The blocks in the flow chart may be executed in the order shown, out of the order shown, or concurrently. Inblock 402, thetransducer 8 generates ultrasound energy at a frequency of at least 20 MHz. - In
block 404, the ultrasound energy is transmitted by the transmitsubsystem 118 into the subject 114 (FIG. 1 ). Inblock 406, the receivesubsystem 120 receives the returnedultrasound echo pulses 104 and communicates the received ultrasound to thecontrol subsystem 127 for processing by theprocessor 134 and thescan converter 129. - In
block 408, the received ultrasound is processed by theprocessor 134 and thescan converter 129, under the direction of thesoftware 123, to generate an image on thedisplay 116. The image has a frame rate of at least 15 frames per second (fps). - Although the high-frequency, high frame-rate ultrasound imaging system has been described with reference to certain specific embodiments, various modifications thereof will be apparent to those skilled in the art without departing from the scope of the high-frequency, high frame-rate ultrasound imaging system as outlined in the claims appended hereto.
Claims (16)
1. A scanhead for use with an ultrasound imaging system, comprising:
a transducer assembly comprising a single element ultrasonic transducer that is configured to generate ultrasound at a frequency of at least 20 megahertz (20 MHz), to transmit at least a portion of the generated ultrasound into a subject and to receive ultrasound energy from the subject;
an elongate member having a proximal end, wherein the elongate member is configured to pivot about a pivot axis spaced from the proximal end, and wherein the transducer assembly is non-rotatably coupled to the proximal end of the elongate member;
a means for oscillating the transducer along a reciprocating convex arcuate path at a frequency of at least 7.5 Hz, wherein a portion of the means for oscillating is fixed relative to the elongate member and moves along a reciprocating arcuate route remote from the reciprocating arcuate path of the transducer such that movement of the portion of the means for oscillating causes a complementary and opposite movement of the transducer, and wherein the reciprocating arcuate path of the transducer is co-planer to the reciprocating arcuate route of the portion of the means for oscillating; and
a means for sensing the spatial position of a proximal end of the portion of the means for oscillating along the reciprocating actuate route to determine the position of the transducer along its arcuate path.
2. The scanhead of claim 1 , wherein the transducer is a broadband transducer.
3. The scanhead of claim 1 , wherein the transducer assembly and at least a portion of the elongate member are located within an enclosed volume, and wherein the enclosed volume is at least partially filled with a fluid.
4. The scanhead of claim 3 , wherein the enclosed volume is partially defined by an acoustically penetrable membrane and wherein the acoustically penetrable membrane is positioned such that at least a portion of the generated ultrasound can pass therethrough the membrane before being transmitted into the subject.
5. The scanhead of claim 4 , wherein the acoustically penetrable membrane comprises a material selected from the group consisting of: polyester, polycarbonate, acrylic, thermoplastic elastomer, silicone elastomer, latex elastomer, Surlyn® ionomer, Surlyn® 8940, Kapton®, polymethyl pentene, TPX® MX-002, TPX® 95, MX-004; Teflon®, Mylar®, polyethylene, polytetrafluoroethylene, polycarbonate, polypropylene, and polyurethane films.
6. The scanhead of claim 1 , further comprising a position encoder configured to determine the position of the transducer along its reciprocating arcuate path.
7. The scanhead of claim 6 , wherein the position encoder is configured such that the position of the transducer can be accurately tracked along the reciprocating arcuate path to within about 1.0 micron (μm) of the actual transducer position.
8. The scanhead of claim 1 , wherein the means for oscillating comprises a limited angle motor.
9. An ultrasound imaging system, comprising:
the scanhead of claim 1; and
a processor configured to process the received ultrasound to provide an image having a frame rate of at least 15 frames per second (fps).
10. The system of claim 9 , wherein the processor is further configured to produce an ultrasound image having a spatial resolution of less than about 100 microns (μm).
11. The system of claim 10 , wherein the processor is further configured to produce an ultrasound image having a spatial resolution of about and between 75-100 microns (μm).
12. The system of claim 10 , wherein the processor is further configured to produce an ultrasound image having a spatial resolution of about and between 30-100 microns (μm).
13. The system of claim 9 , wherein the transducer can be oscillated along the reciprocating arcuate path at a frequency of at least 15 Hz, and wherein the processor is configured to provide an image having a frame rate of at least 30 fps and a spatial resolution of less than about 100 microns (μm).
14. An ultrasound imaging system, comprising:
the scanhead of claim 1;
a processor configured to process the received ultrasound to provide an image having a frame rate of at least 15 frames per second (fps); and
a means for positioning the transducer to within about 1 micron (μm) of a predetermined location along the reciprocating arcuate path.
15. The ultrasound imaging system of claim 14 , wherein the processor is further configured to provide a pulsed-wave Doppler image.
16. The ultrasound imaging system of claim 14 , wherein the processor is further configured to provide an M-Mode image.
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- 2003-10-10 CA CA 2501647 patent/CA2501647C/en not_active Expired - Lifetime
- 2003-10-10 ES ES03776327T patent/ES2402270T3/en not_active Expired - Lifetime
- 2003-10-10 JP JP2005501172A patent/JP4713339B2/en not_active Expired - Lifetime
- 2003-10-10 WO PCT/US2003/032320 patent/WO2004034694A2/en active Application Filing
- 2003-10-10 AU AU2003284096A patent/AU2003284096A1/en not_active Abandoned
- 2003-10-10 EP EP20030776327 patent/EP1465531B1/en not_active Expired - Lifetime
-
2006
- 2006-05-08 HK HK06105370A patent/HK1085109A1/en not_active IP Right Cessation
-
2007
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-
2010
- 2010-04-28 US US12/769,419 patent/US8827907B2/en active Active
-
2013
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2014
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Also Published As
Publication number | Publication date |
---|---|
US7255678B2 (en) | 2007-08-14 |
US20140073929A1 (en) | 2014-03-13 |
WO2004034694A2 (en) | 2004-04-22 |
US20140336512A1 (en) | 2014-11-13 |
AU2003284096A8 (en) | 2004-05-04 |
CA2501647A1 (en) | 2004-04-22 |
US20040122319A1 (en) | 2004-06-24 |
JP4713339B2 (en) | 2011-06-29 |
CA2501647C (en) | 2013-06-18 |
EP1465531A4 (en) | 2005-05-04 |
US8827907B2 (en) | 2014-09-09 |
EP1465531B1 (en) | 2012-12-19 |
HK1085109A1 (en) | 2006-08-18 |
WO2004034694A9 (en) | 2004-06-03 |
US20110021919A1 (en) | 2011-01-27 |
WO2004034694A3 (en) | 2004-07-15 |
EP1465531A2 (en) | 2004-10-13 |
JP2006502828A (en) | 2006-01-26 |
ES2402270T3 (en) | 2013-04-30 |
AU2003284096A1 (en) | 2004-05-04 |
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