Medical Ultrasound Transducers

Abstract

The ultrasonic transducer assembly includes a housing, an acoustic mode converter (AMC) having a first surface exposed by an opening in the housing and a second surface contacting the first surface at a tip provided within the housing and extending obliquely from the tip into the housing, the AMC being wedge-shaped within the housing, the second surface having a recess formed in the second surface, the second surface of the AMC being oriented at a specific oblique angle relative to the first surface of the AMC, and a piezoelectric ultrasonic transducer connected to an electrically tuned circuit resonating at a specific frequency and having a finite bandwidth and provided within the recess in the second surface of the AMC.

Description

[Technical field]

[0001] Embodiments of the present disclosure are directed to ultrasound transducers that generate shear waves that effectively evoke a cascade of cellular functions that promote tissue healing. [Background technology]

[0002] The use of ultrasound waves in the range of 0.5-2.0 MHz is known to treat tissue and bone injuries. The spatial, temporal and frequency parameters of specific acoustic signals have been determined to induce tissue rupture, bone fracture and promote the natural healing of fractures. Summary of the Invention [Problem to be solved by the invention]

[0003] Embodiments of the present disclosure provide an acoustic transducer that can exogenously and synchronously apply both acoustic longitudinal and shear stress waves to the extracellular matrix (ECM) of bone cells to increase integrin responses and therefore the associated mechano-biochemical transduction efficiency of the bone healing process. [Means for solving the problem]

[0004] According to one embodiment of the present disclosure, an ultrasonic transducer assembly is provided, comprising: a housing, a first surface exposed by an opening in the housing, a second surface abutting the first surface at a tip disposed within the housing and extending obliquely from the tip into the housing, a wedge-shaped acoustic mode converter (AMC) within the housing, the second surface having a recess formed within the second surface, the second surface of the AMC being oriented at a specific oblique angle relative to the first surface of the AMC, and a piezoelectric ultrasonic transducer disposed within the recess in the second surface of the AMC, connected to an electrically tuned circuit that resonates at a specific frequency and has a finite bandwidth. The piezoelectric ultrasonic transducer has a back surface electroded with a metal plating in a uniform or elliptical pattern, protruding from the recess and loaded with a material that controls forward scattering amplitude and absorption cross section, and a front surface similarly electroded within the recess. The front surface forms a ground plane and includes a matching layer over the ground plane of one or more materials. Tuned ultrasound transducers transmit oblique acoustic waves of electrical signals designed for fracture healing.

[0005] According to a further embodiment of the present disclosure, the ultrasonic transducer transmits acoustic waves at a resonant center frequency between 0.1 MHz and 10 MHz.

[0006] According to a further embodiment of the present disclosure, the ultrasonic transducer transmits acoustic waves at frequencies between 0.5 MHz and 2 MHz.

[0007] According to a further embodiment of the present disclosure, the ultrasonic transducer has a power output of 30 to 60 mW / cm 2 Transmit acoustic waves for fracture healing at 1 MHz with a spatial-averaged and temporal-averaged intensity of 100 Hz, a pulse width of 0.1 to 10 milliseconds, a duty ratio of 10 to 50%, and a pulse repetition frequency of 10 KHz or less.

[0008] According to a further embodiment of the present disclosure, the piezoelectric ultrasonic transducer further comprises one or more of the piezoelectric elements. According to a further embodiment of the present disclosure, the piezoelectric elements include PZT-4, PZT-5H, PZT-7H, and PZT-8.

[0009] According to a further embodiment of the present disclosure, the composition of the embedded AMC includes a silicone rubber polymer and a thin film silicone primer that adheres the silicone rubber polymer to a non-silicone surface.

[0010] According to further embodiments of the present disclosure, the silicone rubber polymer includes one of RTV-60, RTV-31, RTV-88, RTV-511, RTV-560, and RTV-577. The thin film silicone primer includes one of SS4004P and SS4155.

[0011] According to a further embodiment of the present disclosure, the silicone rubber polymer exhibits a specific critical angle based on the longitudinal velocity and shear velocity of the silicone rubber polymer according to Snell's Law to generate maximum shear waves in the bone tissue.

[0012] According to a further embodiment of the present disclosure, the maximum shear wave has a beam nonuniformity ratio (BNR) of 6.0 or less for medical ultrasound.

[0013] According to a further embodiment of the present disclosure, the maximum shear wave has a beam nonuniformity ratio (BNR) of 5.0 or less for medical ultrasound.

[0014] According to a further embodiment of the present disclosure, the maximum shear wave has a beam nonuniformity ratio (Rbn) of 4.0 or less for medical ultrasound.

[0015] According to a further embodiment of the present disclosure, the maximum shear wave has a beam nonuniformity ratio (Rbn) of 3.0 or less for medical ultrasound.

[0016] According to a further embodiment of the present disclosure, the maximum shear wave input to the transducer is 24 Vpp at a frequency of 1 MHz to produce a Mechanical Index (MI) of 0.5 or less.

[0017] According to a further embodiment of the present disclosure, the maximum shear wave input to the transducer is 24 Vpp at a frequency of 1 MHz to produce a Mechanical Index (MI) of 0.2 or less.

[0018] According to a further embodiment of the present disclosure, the ultrasonic transducer has an elliptical electrode pattern on a front surface of the ultrasonic transducer that forms a circular effective radiating area in the oblique plane at an angle based on the major axis of the ellipse, the minor axis of the ellipse, and the eccentricity of the ellipse to enhance spatial and temporal measurement accuracy in angle.

[0019] According to a further embodiment of the present disclosure, the tuning circuit is part of an output stage of a high efficiency transmitter power switching amplifier.

[0020] According to further embodiments of the present disclosure, the power switching amplifier has a class D, class E or class F configuration.

[0021] According to a further embodiment of the present disclosure, an ultrasound transducer assembly includes a gel sensor, part of a microcontroller unit (MCU), for detecting air bubbles due to coupling between a first surface of the AMC and non-propagating biological tissue, and processing circuitry integrated into the transducer housing for sampling amplitude and phase coherence at the surface of the AMC / skin interface.

[0022] According to a further embodiment of the present disclosure, the ultrasonic transducer assembly includes an external test meter that determines the total transmitted rms power by integrating the sum of the spatial acoustic beam orientation of the ultrasonic transducer and the conjugate plane of the externally applied AMC, whose output is normalized and sent to the external test meter. [Brief description of the drawings]

[0023] [Figure 1]1 is a photograph showing an acoustic mode converter (AMC) oriented to show its interior surface and a second AMC applied externally to the transducer, according to an embodiment of the present disclosure. [Diagram 2] 1 is a photograph of an implantable AMC with an ultrasound transducer according to an embodiment of the present disclosure. [Diagram 3] 1A-1C are diagrams showing multiple views of an ultrasonic transducer assembly using a plastic housing according to an embodiment of the present disclosure. [Figure 4] 1 is a table of measured electroacoustic properties of an ultrasound transducer according to an embodiment of the present disclosure. [Diagram 5] 5A-C show (A) a typical Z-scan, (B) a typical XY-scan at 3 mm, and (C) a typical XY-scan at 34.8 mm, according to an embodiment of the present disclosure. [Figure 6] 1 is a table of typical measurements of non-thermal nonlinear ultrasonic behavior in biological tissue, according to an embodiment of the present disclosure. [Figure 7] 1 illustrates a means for measuring the root-mean-square (rms) acoustic power transmitted by an ultrasonic transducer using a matching AMC rotated 180° relative to the unit under test to normalize the beam path length, according to one embodiment of the present disclosure. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0024] Figure 1 is a photograph of an acoustic mode converter (AMC) 100 test fixture. On the right, the AMC 100 is oriented to show a recess 110 that can receive a transducer. On the left, the AMC is shown on its side, showing a transducer 120 received in the recess 110 and a beveled surface 140 facing the transducer 120. A power cord 150 is attached to the transducer. This is the simplest approach to oblique beam steering. The bevel angle can control the relative amounts of longitudinal and shear energy propagating in bone tissue and the amount of thermal energy generated.

[0025] According to one embodiment of the present disclosure, to determine the balance between shear and longitudinal modes, the resonating biological structure is modeled as a parallel four-layer system, with the three outermost layers, i.e., skin, fat, and muscle, representing viscous fluids and the fourth innermost layer, i.e., bone, representing a viscoelastic solid. Bone tissue needs to be characterized for both viscous and elastic components to meaningfully affect fracture repair.

[0026] According to one embodiment, acoustic waves propagated within bone propagate as both shear and longitudinal waves, referred to herein as Bi-Model Acoustic Signals (BMAS).

[0027] Snell's law tells us that when waves travel from a slower material to a faster material, there exists an angle of incidence called the first critical angle, where the refraction angle of the longitudinal wave is 90 degrees. Once the angle of incidence is initially greater than the critical angle, the energy of the shear wave propagating into the material becomes greater than the energy of the longitudinal wave, and increases as the oblique angle increases. For most materials, there also exists an angle of incidence where the refraction angle of the shear wave is nearly 90 degrees. This is called the second critical angle.

[0028] Furthermore, in physical acoustics, when a plane wave is obliquely incident at approximately the second critical angle and is incident on a nearly planar interface between a viscous fluid and a viscoelastic solid such as bone, shear waves will grow and propagate along and just beneath the periosteal surface of the bone. Noting that acoustic shear waves are more "lossy" than longitudinal waves, the spatially-averaged-temporal-averaged (SATA) intensity levels of shear waves should be at least 10 dB / cm higher than the intensity levels required for longitudinal waves in the 0.5-2 MHz region to enhance healing efficiency. 2 It needs to be increased.

[0029] Proof-of-concept (POC) torsion testing in adult rabbits undergoing surgical bilateral fibular osteotomies showed that the test device 100 of FIG. 1 with BMAS excitation according to embodiments outperformed current U.S. Food and Drug Administration (FDA)-approved devices after undergoing treatment (Non-Patent Document 1). The dominant shear wave mode in the test device was achieved with an external AMC 110 consisting of a silicone rubber wedge with a 31.5 degree oblique angle, and Bone Growth Stimulation (BGS) appeared to respond favorably to periosteal healing over endosteal healing. The AMC according to embodiments is composed of a silicone rubber, Room Temperature Vulcanized (RTV) composition with an acoustic impedance in the range of 1.30-1.90 MRayls.

[0030] According to one embodiment, the RTV material is selected because its acoustic impedance closely matches that of the target biological tissue. In addition, the RTV material can be easily molded to produce a cant angle close to the second critical angle for maximum shear volume in the desired bone tissue. In the embodiment, RTV-60 silicone rubber is used, but the embodiment is not limited thereto, and in other embodiments, others in the RTV family can be used, such as, but not limited to, RTV-31, RTV-88, RTV-511, RTV-560, RTV-577, etc. However, any material whose acoustic impedance closely matches that of biological tissue can be used for the AMC.

[0031] 2 shows a barrel ultrasonic transducer assembly 200 including a radiating surface embedded with a housing fixture 210 and an AMC wedge 220 of RTV-60 silicone rubber to produce oblique transmission. The typical barrel ultrasonic transducer assembly 200 shown in FIG. 2 is a 1 mm diameter 12 is cylindrical with a circular cross section perpendicular to the axis of the cylinder, but embodiments are not limited to these dimensions and may be larger if desired. Although the housing fixture 210 shown in FIG. 2 is cylindrical in shape and has a circular cross section perpendicular to the axis of the cylinder, embodiments are not limited thereto and the housing fixture 210 may have other cross sections, such as rectangular, hexagonal, or pentagonal, in other embodiments. Additionally, an exemplary material for making the barrel ultrasonic transducer assembly 200 is a hard, machinable, moldable plastic. The visible front side of the embedded AMC wedge 220 corresponds to the beveled surface 140 of the AMC in FIG. 1. RTV-60 is a two-part compound with a 24 hour room temperature cure 0.5 wt % DBTDL (dibutyltin dilaurate). The AMC wedge 220 includes a recess corresponding to the recess 110 of FIG. 1 on the opposite side of the visible side in FIG. 2, with a piezoelectric ceramic transducer embedded in the recess of the AMC wedge 220. The piezoelectric ceramic transducer includes a non-silicone matching layer and requires the use of a uniform thin adhesive film of a silicone primer such as SS4004P or SS4155 to embed the transducer matching layer into the AMC at an angle of 31.50. A maximum apex thickness of 2mm is preferred, but embodiments are not limited thereto. A thinner apex thickness may produce a weaker AMC, while a thicker apex thickness may require additional power to compensate for increased losses in the SATA due to RTV absorption. The 31.5 degree beam pattern is scanned at a depth of approximately 8.5mm from the crystal center. RTV-60 is a hospital grade elastomer that is non-toxic and blood impermeable, with an acoustic attenuation of 3.64dB / cm at 1.0MHz, an acoustic impedance of 1.36MRayls, a longitudinal velocity of 919m / s, and a density of 1478kg / m 3 These acoustic parameters are in excellent agreement with the reported data from Selfridge (Non-Patent Document 2).

[0032] 3 shows cross-sectional and front views of an ultrasound transducer assembly 300, including a piezoelectric transducer 310 and a housing 320, according to an embodiment. The housing 320 contains the piezoelectric transducer 310 with an electroded ground plane on its front surface covered with a 1 / 4 wave matching layer 311, on which an embedded AMC 330 is mounted.

[0033] The transducer elements are tilted at an angle of 31.5 with respect to the front surface of the housing, which matches the wedge angle of the embedded AMC 330. The front view shows the transducer 310 with the AMC 330 removed, also exposing the top inner surface 321 of the housing 320. An indicator 380 on the housing shows the direction of beam steering by the built-in AMC. The housing dimensions described above with reference to Figure 2 allow for transmission at the desired oblique angles without backscattering interference.

[0034] The space 325 behind the back surface 312 of the transducer 310 is air filled, however, it is also well known in the art of transducer design that controlling the acoustic impedance of the back surface material can greatly affect the sensitivity of the detection and measurement parameters. Non-limiting examples of piezoelectric elements include PZT-4, PZT-5H, PZT-7H, PZT-8, etc. The piezoelectric transducer 310 also includes a tuning electrical circuit 370.

[0035] The back of the housing 320 has a cable housing 350 and an electrical tuning circuit 370 connected to the cable housing 350 and to the transducer 310. The back 312 of the piezoelectric transducer 310 may be covered with a uniform electrode pattern 312 or an elliptical electrode pattern 313. The tuning circuit as shown in FIG. 3 is a series RLC network to transform the complex impedance of the transducer into a 50 ohm resistor that loads the front output stage of the driving transmitter high power switching amplifier. It is well known in the art of electronics design that the series RLC shown can be replaced with an equivalent pi and T network to facilitate certain operational considerations (balanced, unbalanced, heat dissipation, Q, etc.).

[0036] In some embodiments, the ultrasound transducer assembly 300 includes a gel sensor 395 residing in a microcontroller unit (MCU) 390 and auxiliary processing circuitry 360 that samples the amplitude and phase coherence in front of the AMC / skin interface. The gel sensor 395 detects the effects of air bubbles that may prevent efficient coupling of the first surface of the AMC with the biological tissue. An example of a gel sensor 395 is disclosed in U.S. Patent No. 6,261,249, the contents of which are incorporated herein by reference in their entirety.

[0037] Additionally, the electrical tuning circuit 370 of the gel sensor 395 may be part of the output stage of the transmitter power switching amplifier and may be in any configuration, including but not limited to Class D, Class E, or Class F. Isolating the power MOSFET from the tuning output stage may provide performance benefits related to battery size, heat dissipation, and associated miniaturized transmitter design to improve reliability.

[0038] The electroacoustic parameters of the three tested ultrasonic transducers are shown in Table 1, which is shown in Figure 4. Figure 4 shows the serial number (S / N), center frequency, -6 dB bandwidth, -20 dB pulse width, and electrical impedance Z of the transducers. elect1 is a table of measured electroacoustic properties of tested ultrasound transducers according to embodiments of the present disclosure, including: an exemplary ultrasound transducer transmits acoustic waves at a resonant center frequency of 0.1 MHz to 10 MHz; another exemplary ultrasound transducer transmits acoustic waves at frequencies from 0.5 MHz to 2 MHz; an ultrasound transducer according to one embodiment transmits acoustic waves at a resonant center frequency of 30 to 60 mW / cm 2 Transmit acoustic waves for fracture healing at 1 MHz, with a spatial-averaged and temporal-averaged intensity of 100 nm, a pulse width of 0.1-10 ms, a duty ratio of 10-50%, and a pulse repetition frequency of 10 KHz or less.

[0039] The silicone rubber polymer of AMC330 exhibits a second critical angle based on the longitudinal direction and shear rate of the silicone rubber polymer based on Snell's law, which generates a maximum shear wave in the bone tissue. In an embodiment, the maximum shear wave has a beam nonuniformity ratio (BNR) of 6.0 or less for medical ultrasound. In an embodiment, the maximum shear wave has a beam nonuniformity ratio (Rbn) of 4.0 or less for medical ultrasound. The maximum shear wave generates a mechanical index (MI) of 0.5 or less and applies 24 Vpp to the transducer at a frequency of 1 MHz. In an embodiment, the maximum shear wave has a beam nonuniformity ratio (BNR) of 5.0 or less for medical ultrasound. In an embodiment, the maximum shear wave has a beam nonuniformity ratio (Rbn) of 3.0 or less for medical ultrasound. The maximum shear wave generates a mechanical index (MI) of 0.2 or less and applies 24 Vpp to the transducer at a frequency of 1 MHz.

[0040] 5A-C show beam plots of root mean square voltage (VRMS) as a function of pixel number for (A) Z-scan, (B) xy-scan at 3 mm, and (C) xy-scan at 34.8 mm for a typical ultrasound transducer (S / N5985) according to one embodiment of the present disclosure. Standard test protocols for determining the Effective Radiation Area (ERA) or Area for effective radiation (Aer) call for a raster scan perpendicular to the beam surface 5 mm (for ERA) and 3 mm (for Aer) from the faceplate, respectively.

[0041] For oblique transmission, the following figures are typical of an ultrasonic transducer designed and manufactured as represented by serial number 5985. Figure 5A shows the Fresnel zone in the first 20 mm of a 1D scan, actively progressing to the in-phase Fraunhofer region with a maximum at 34.8 mm, where the in-phase wave motion slowly decays as 1 / z with increasing propagation range. As seen in Figures 5B-C, the 2D-oblique beam plots of the test transducer at z=3.0 and z=34.8 mm in the xy plane did not identify any acoustic "hot spots".

[0042] The most notable exception to these diagrams is the shape of the focal region, which is circular in the near field and elliptical in the far field. If the uniformly electroded face of the transducer is electroded in an elliptical pattern, then at the unique oblique plane in the far field, a circular emitting beam pattern is produced at an angle based on the major axis of the ellipse, the minor axis of the ellipse, and the eccentricity of the ellipse, improving the space-time measurement accuracy at that angle. This tends to have a constant false alarm rate on reception, facilitating the detection of echoes and the extraction of information from a specific illuminated region of interest (ROI) along the axis of maximum response.

[0043] Figure 6 shows typical measurements of the non-thermal nonlinear ultrasonic behavior in biological tissue for the ultrasound transducers tested, namely, the transducer serial number, mechanical index (MI; MPa / MHz 1 / 2 ), effective radiation area (Aer; cm 2 ), and Table 2, a table of beam nonuniformity factors (Rbn) that establish safety standards for medical diagnostic and therapeutic ultrasound.

[0044] The ultrasonic transducer in Figure 2 was excited with the parameters shown in Table 1, a resonant frequency of 1 MHz, a 6 dB bandwidth of 400 kHz, a constant envelope, a pulse width of 200 microseconds, a pulse repetition frequency of 1 kHz, a duty cycle of 20%, and an input drive voltage to the transducer of 24.0 Vpp, and tested using a computer-controlled measurement system. <Technical background> (Mechanical Index (MI)) MI is a measure of the destructive behavior of ultrasound induced in biological tissues by cavitation effects, and is intended for B-mode short pulse, low duty ratio (<2%) diagnostic imaging, which often results in high peak pressures. The FDA requires that diagnostic and therapeutic devices have an MI of less than 0.7 in non-scanning mode, below which cavitation (in theory) does not occur, and requires that the maximum measured value be displayed on the device label. It is assumed that pockets of stabilized gas or free bubbles exist in vivo, but this is not yet known clinically. (Beam nonuniformity ratio, (BNR, Rbn); (ERA / Aer)) BNR / Rbn is a measure of possible acoustic hot spots in the radiated field, [max I SPTA / I SATA ], where [max I SPTA] is the acoustic axial distance of maximum pressure of the unfocused transducer, approximately equal to (transducer diameter)2 / (4 × wavelength λ). ERA is the width of the beam intensity profile function at the -13 dB point at a distance of 5 mm from the transducer axis. Aer is the width of the beam intensity profile function at the -10 dB point at a distance of 3 mm from the transducer axis. <Test Method> (Mechanical index) The definition of MI is the peak rarefactional pressure (p r ; MP a ) divided by the square root of the central signal spectrum frequency (f; MHz):

[0045]

number

[0046] The protocol for measuring MI is as follows: 1. Measure the pulse intensity integral (PII) of the sound field along the MRA of the transducer. PII is calculated as:

[0047]

number

[0048] where ρ is the density and c is the speed of sound propagation in the fluid. 2. Measure the negative pressure at the position of maximum PII.

[0049] 3. Divide the pressure in equation 2 by the square root of the signal resonant frequency. (Beam nonuniformity rate) The steer beam from the ultrasound transducer in water is at an angle of approximately 52.3 degrees from the normal to the faceplate. Tests were performed by raster scanning a plane as close to the surface as possible, and ERA and Aer were calculated at 5mm and 3mm, respectively. The FDA requires that the BNR or Rbn, of therapeutic devices be less than 8.0, and that the maximum measured value be indicated on the device label.

[0050] BNr and Rbn were calculated using the following Equations 3 and 4:

[0051]

number

[0052]

number

[0053] Here, the coefficient cosθ is called the oblique angle coefficient in sonar and radar, and I spta is the maximum intensity detected by the hydrophone in situ, and θ is the measured angle of the beam with respect to the faceplate normal, i.e., the angle between the z axis and the direction of propagation.

[0054] In actual beam plot measurements, the difference between the RTV material velocity at the faceplate (919 m / s) and the water velocity (1492 m / s) results in a deflection of the beam of approximately θ = 52.3 degrees with respect to the normal to the faceplate. The Aer value in Table 2 includes a slope factor of cos 52.3 degrees (= 0.6115).

[0055] The transducers tested exhibited an MI of ≦0.13. The 1992 AIUM-NEMA standard suggests an acceptable MI of less than 0.7 in non-scanning mode, below which cavitation (in theory) does not occur. Clinical studies to date have shown that an MI of less than 0.5 is free of non-thermal adverse biological effects. (Non-Patent Document 6) The FDA and the International Electrotechnical Commission (IEC) require that the maximum measured values ​​of BNR and Rbn for therapeutic devices be less than 8.0 and that the maximum measured values ​​be indicated on the labeling of the device (Non-Patent Document 5, Non-Patent Document 6). The tested transducers showed BNR ≦ 5 and Rbn ≦ 3 from Table 2. It should be noted that Aer and Rbn should be independent of the driving voltage, assuming that the transducer operates in the linear region of acoustic propagation, whereas MI changes with the driving voltage. Using the test conditions and methods described in IEC 1689, the Rbn results reported in Table 2 "achieved a measurement uncertainty of ± 15% (at the 95% confidence level)" (Non-Patent Document 4).

[0056] Moreover, the active elements can be made of composites of such materials with polymers, voids and / or metal components. Moreover, active elements made of such materials can generate low frequencies through stretching effects that can be achieved with unimorphs, monomorphs, bimorphs, cymbals, moonies, thunders, rainbows, cerambos, etc., as known to those skilled in the art. Moreover, the frequencies mentioned herein can be generated by mechanical vibration of air molecules or molecules of a medium in contact with the human body using speakers, buzzers, tuning forks, and / or any non-active mechanical vibration elements driven by the above active elements. Moreover, the low bone formation frequencies disclosed herein can also be generated by transducers consisting of mechanically and electrically micromachined ultrasonic transducers (MUTs). Examples of such MUTs include mechanically and electrically micromachined capacitive ultrasonic transducers (CMUTs) and mechanically and electrically micromachined piezoelectric ultrasonic transducers (PMUTs). The CMUTs and PMUTs can be independent transducers or integrated onto electronic circuit boards that drive such MUTs. AMC materials can be thermoplastic urethane rubber, polyurethane, or silicone rubber.

[0057] Figure 7 shows an apparatus 700 for testing the rms acoustic power from an ultrasonic transducer with a given transducer assembly 720 of embedded AMCs. Figure 7 shows an internal cross section of Figure 2 showing the piezoelectric transducer 721 and AMC 722 in contact with their respective matching AMCs 732 rotated 180° relative to the transducer under test 720 to normalize the path length of the beam. The two AMCs 722, 732 are separated by a coupling gel 739. The test assembly 700 includes a galvanometer test unit 740 and a signal conditioner 741 which may consist of linear low noise preamplifiers, band pass filters and a matching network with the tester 740 required for accurate and stable measurement of the output signal from the test piezoelectric transducer 731.

[0058] In operation, the transducer assembly 720 generates and propagates an AMC to the AMC. Due to the fact that the AMC 732 is rotated 180 degrees relative to the transducer assembly 720, the path length of the ultrasonic energy at the output of the AMC 731 is approximately the same, with minimal refraction through the AMC wedges 722, 732. Thus, the piezoelectric element 731 responds to the degree of coherence of the rms acoustic energy of the acoustic transmission that stimulates the piezoelectric element 731 to generate an electrical signal that is measured by a calibrated galvanometer.

[0059] The design and manufacturing approach according to embodiments can feature at least ten unique features for obtaining bone stimulation for healing fractures, as follows:

[0060] a. Acoustically and mechanically couple the transducer and AMC. b. Using AMC to beam steer an acoustic wave to a region of interest in biological tissue, specified by Snell's Law as the second critical angle.

[0061] c. An acoustic mode converter (AMC) is incorporated into the transducer housing, which is made of a silicone polymer from an RTV, such as RTV-60. Other materials from the RTV family can also be used.

[0062] d. Producing a Beam Nonuniformity Ratio (FDA; BNR) of 5.0 or less for medical therapeutic ultrasound.

[0063] e. For medical ultrasound treatment applications, the beam nonuniformity ratio (IEC; Rbn) must be 3.0 or less.

[0064] f. Producing a Mechanical Index (MI) of 0.2 or less for both medical diagnostic and therapeutic applications.

[0065] g. The transducer electrode pattern is elliptical to provide a circular effective radiation area for measuring acoustic intensity at an oblique plane on the MRA, improving the measurement accuracy of spatial position parameters.

[0066] h. Includes a tuning network representing the output stage of a high efficiency switching power amplifier present in the driving transmitter and may include a simple tuning inductor present in the transducer. The increased efficiency can reduce battery requirements and facilitate ultra-compact transmitter designs.

[0067] i. Use a gel sensor that resides partially in a microcontroller unit (MCU) in the transmitter and supporting processing circuitry in the transducer that samples the amplitude and phase coherence in front of the AMC / skin interface.

[0068] j. To normalize the beam path length driving the calibrated galvanometer 740, the conjugate AMC 731-signal conditioner 741 assembly is used to measure the total rms acoustic power from the transducer under test 720.

[0069] While certain exemplary embodiments of the present disclosure have been specifically described herein, it will be apparent to those skilled in the art to which the embodiments of the present disclosure pertain, that variations and modifications of the various embodiments shown and described herein can be made without departing from the spirit and scope of the present disclosure. [Prior art documents] [Non-patent literature]

[0070] [Non-Patent Document 1] Machado P, Li J., Blackman R., Liu JB, Kepler C, Fang T, Muratore R, Winder J, Winder, A, Forsberg F, “Comparison between clinically available low intensity pulsed ultrasound (LIPUS) and a novel bimodal acoustic signal system accelerating fracture healing,” submitted to TUFFC-manuscript no. 10470-2020, under review. [Non-Patent Document 2] Selfridge, AR, "Approximate Material Properties in Isotropic Materials," IEEE Transactions on Sonics and Ultrasonics, Vol. SU-32, No. 3, May 1985, pp. 381-384. [Non-Patent Document 3] IEC 62359:2010 + AMD1:2017 CSV: Ultrasonics - Field characterization - Test methods For the determination of thermal and mechanical indices related to medical indices related to medical diagnostic ultrasonic fields。

Non - Patent Document 4

Non - Patent Document 5

Non - Patent Document 6

Claims

1. 1. An ultrasonic transducer assembly comprising: A housing and a first surface exposed by an opening in the housing; and a second surface that contacts the first surface at a tip portion provided within the housing and extends obliquely from the tip portion into the housing; an acoustic mode converter (AMC) having a wedge shape within the housing, the second surface having a recess formed therein, the second surface of the AMC being oriented at a particular oblique angle relative to the first surface of the AMC; Resonates at a specific frequency, has a finite bandwidth, a piezoelectric ultrasonic transducer connected to an electrically tuned circuit and disposed within the recess in the second surface of the AMC; Equipped with The piezoelectric ultrasonic transducer includes: a back surface electroded with metal plating in an elliptical pattern, protruding from said recess, and loaded with a material that controls scattering amplitude and absorption cross section; a front surface, also electroded within said recess; having the front surface forms a ground plane and includes a matching layer over the ground plane of one or more materials; Tuned ultrasound transducers transmit oblique acoustic waves of electrical signals designed for fracture healing. An ultrasonic transducer assembly.

2. The ultrasonic transducer transmits acoustic waves at a resonant center frequency of 0.1 MHz to 10 MHz.

2. The ultrasonic transducer assembly of claim 1.

3. The ultrasonic transducer transmits acoustic waves at a frequency between 0.5 MHz and 2 MHz.

3. The ultrasonic transducer assembly of claim 2.

4. The ultrasonic transducer includes: 30~60mW / cm ２ and the spatial and temporal average intensity of A pulse width of 0.1 to 10 milliseconds; A duty ratio of 10 to 50%; A pulse repetition frequency of 10 KHz or less; 1. Transmitting acoustic waves for fracture healing at 1 MHz; 2. The ultrasonic transducer assembly of claim 1.

5. The piezoelectric ultrasonic transducer has one or more piezoelectric elements.

2. The ultrasonic transducer assembly of claim 1.

6. The piezoelectric element group includes PZT-4, PZT-5H, PZT-7H, and PZT-8.

6. The ultrasonic transducer assembly of claim 5.

7. The composition of the embedded AMC includes a silicone rubber polymer and a thin film silicone primer that adheres the silicone rubber polymer to a non-silicone surface.

2. The ultrasonic transducer assembly of claim 1.

8. the silicone rubber polymer comprises one of RTV-60, RTV-31, RTV-88, RTV-511, RTV-560, and RTV-577; The thin film silicone primer includes either SS4004P or SS4155; 8. The ultrasonic transducer assembly of claim 7.

9. The silicone rubber polymer exhibits a specific critical angle based on the longitudinal velocity and shear velocity of the silicone rubber polymer according to Snell's Law to generate maximum shear waves in bone tissue.

8. The ultrasonic transducer assembly of claim 7.

10. The maximum shear wave has a beam nonuniformity ratio (BNR) of 6.0 or less for medical ultrasound.

10. The ultrasonic transducer assembly of claim 9.

11. The maximum shear wave has a beam nonuniformity ratio (BNR) of 5.0 or less for medical ultrasound.

11. The ultrasonic transducer assembly of claim 10.

12. The maximum shear wave has a beam nonuniformity ratio (Rbn) of 4.0 or less for medical ultrasound.

10. The ultrasonic transducer assembly of claim 9.

13. The maximum shear wave has a beam nonuniformity ratio (Rbn) of 3.0 or less for medical ultrasound.

13. The ultrasonic transducer assembly of claim 12.

14. The maximum shear wave is generated at a frequency of 1 MHz and a mechanical index (MI) of 0.5 or less with a 24 Vpp input to the transducer.

10. The ultrasonic transducer assembly of claim 9.

15. The maximum shear wave is generated by inputting 24 Vpp to the transducer at a frequency of 1 MHz to produce a mechanical index (MI) of 0.2 or less.

15. The ultrasonic transducer assembly of claim 14.

16. The ultrasonic transducer includes: an elliptical electrode pattern on the front surface of the ultrasonic transducer, forming a circular effective radiation area within the inclined surface at an angle based on the major axis of the ellipse, the minor axis of the ellipse, and the eccentricity of the ellipse, thereby increasing the accuracy of measurement of time and space at the angle; having an electrode pattern, 2. The ultrasonic transducer assembly of claim 1.

17. the electrical tuning circuit being part of an output stage of a high efficiency transmitter power switching amplifier; 2. The ultrasonic transducer assembly of claim 1.

18. The power switching amplifier has a class D, class E, or class F configuration.

20. The ultrasonic transducer assembly of claim 17.

19. Part of the Microcontroller Unit (MCU) the first surface of the AMC; and Skin and a gel sensor for detecting air bubbles due to the bonding of a processing circuit that samples the amplitude and phase coherence at the surface of the AMC / skin interface and is integrated into the housing of the transducer; The ultrasonic transducer assembly of claim 1 further comprising:

20. An external test meter for measuring (root mean square) rms sound power, comprising a conjugate AMC for normalizing beam path length and a signal conditioner. The ultrasonic transducer assembly of claim 1 further comprising:

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