CN109231150B - Combined film pMUTs and preparation method thereof - Google Patents
Combined film pMUTs and preparation method thereof Download PDFInfo
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- CN109231150B CN109231150B CN201811037084.0A CN201811037084A CN109231150B CN 109231150 B CN109231150 B CN 109231150B CN 201811037084 A CN201811037084 A CN 201811037084A CN 109231150 B CN109231150 B CN 109231150B
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- B81—MICROSTRUCTURAL TECHNOLOGY
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- B81B7/00—Microstructural systems; Auxiliary parts of microstructural devices or systems
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- B81—MICROSTRUCTURAL TECHNOLOGY
- B81B—MICROSTRUCTURAL DEVICES OR SYSTEMS, e.g. MICROMECHANICAL DEVICES
- B81B3/00—Devices comprising flexible or deformable elements, e.g. comprising elastic tongues or membranes
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- B81C—PROCESSES OR APPARATUS SPECIALLY ADAPTED FOR THE MANUFACTURE OR TREATMENT OF MICROSTRUCTURAL DEVICES OR SYSTEMS
- B81C1/00—Manufacture or treatment of devices or systems in or on a substrate
- B81C1/00349—Creating layers of material on a substrate
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- B81—MICROSTRUCTURAL TECHNOLOGY
- B81C—PROCESSES OR APPARATUS SPECIALLY ADAPTED FOR THE MANUFACTURE OR TREATMENT OF MICROSTRUCTURAL DEVICES OR SYSTEMS
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- B81C1/00436—Shaping materials, i.e. techniques for structuring the substrate or the layers on the substrate
Abstract
The invention provides a combined film pMUTs and a preparation method thereof, wherein a combined film structure consists of a circular film and an annular film which surrounds the circumference of the circular film and is concentric with the circular film, and the whole structure of the combined film structure sequentially comprises an upper electrode, a vibration film piezoelectric driving layer, a lower electrode, a vibration film structure layer, a film supporting structure and a substrate structure from top to bottom; when the ultrasonic wave generator is used in an ultrasonic wave transmitting working mode, the circular film and the annular film are excited with a certain phase difference, so that the coupling effect between the circular film and the fluid medium and between the circular film and the annular film is caused, and the ultrasonic wave transmitting power of the unit is greatly improved; when the ultrasonic receiving device is used in an ultrasonic receiving working mode, the circular film and the annular film vibrate to generate detectable electric signals, and meanwhile, the wide bandwidth receiving performance of ultrasonic is realized through the resonance frequency deviation of the structures of the circular film and the annular film in a fluid medium. The combined thin film structure pMUTs provided by the invention has high transmitting power and wide bandwidth receiving performance.
Description
Technical Field
The invention relates to the technology of MEMS (Micro-electro mechanical Systems) Ultrasonic transducers, in particular to pMUTs (piezoelectric Micro-machined Ultrasonic transducers) with high electromechanical coupling coefficient and a preparation method thereof.
Background
The ultrasonic transducer has important application value for non-invasive in-vivo medical diagnosis imaging. Conventional ultrasonic transducers are fabricated from a piezoceramic material, such as lead zirconate titanate (PZT) or a PZT polymer composite, that is diced or laser cut to form a one-or two-dimensional array of individual cells. Acoustic lenses, matching layers, backing layers, and electrical interconnects (e.g., flexible cables, metal pins/wires), etc., are attached to each transducer element to form a transducer assembly or probe, which is then connected to a control circuit with a harness or cable that contains individual wires that drive and receive signals from each individual element. An important goal of current research in ultrasound transducer technology is to improve transducer performance and integration with control circuitry while reducing transducer size, power consumption, and signal loss due to cabling. These factors are particularly important for the two-dimensional array required for three-dimensional ultrasound imaging.
Miniaturization of transducer arrays is particularly important for catheter-based 2D array transducers. The technical challenges are the complex fabrication, high cost, limited performance, etc. of conventional 2D transducer arrays. Commercial 2D transducer probes are limited to arrays with large cell pitches (200 to 300 μm) and operating frequencies less than 5 MHz. The small size of these cells greatly reduces the capacitance of the cell to less than 10pF, presenting a significant challenge to match the electrical impedance of the system electronics. Furthermore, the production of 2D array transducer probes for catheter-based intravascular or intracardiac imaging probes has not been commercialized. In order to obtain sufficient resolution, a frequency of 10MHz or more should be used, and in order to obtain sufficient imaging performance, the cell pitch should be smaller than the wavelength, so that an element pitch of 100 μm or less is desirable. In addition, higher operating frequencies require thinner piezoelectric layers in the transducer. Conventional transducer arrays have not heretofore been able to meet these requirements with low cost manufacturing processes and adequate imaging performance.
Compared to conventional piezoelectric ceramic transducers, pMUTs has the following advantages: ease of manufacture and scalability, particularly for smaller size, higher density 2D arrays; integration and interconnection is simpler for 2D arrays; for a wider operating frequency range, the design flexibility of the transducer is greater; the unit capacitor is larger, so that the unit capacitor has smaller source impedance and is better matched with an electronic device. Real-time 3D imaging systems require 2D arrays, while piezoelectric ceramic transducers cannot achieve smaller catheter probes (2-3 mm diameter or smaller). Another type of capacitive micromachined ultrasonic transducer (cmut) is driven to emit ultrasound by electrostatic force between a membrane and a substrate. However, these devices require multiple cells in parallel to provide adequate sound pressure output, so there is a limit to miniaturization of the 2D array.
There are functional and structural differences between cMUTs and pMUTs. Because pMUTs have a larger energy transducing mechanism (i.e., the piezoelectric layer), pMUTs typically have a greater ultrasound transmit power than cMUTs. At a frequency of 8MHz, a 75 micron wide array of pMUTs2D can produce a sound pressure output of 1MPa to 5 MPa. Conventional transducer arrays can produce sound pressures greater than 1MPa but require much larger cell sizes and operate at lower frequencies. The typical sound pressure output of cMUTs 2D array elements is much less than 1 MPa. The cells in the pMUTs array also have a larger capacitance (on the order of 100-. The capacitance of the conventional transducer array elements is less than 10pF and the capacitance of the cMUTs elements is less than 1 pF.
pMUTs requires lower operating voltages than conventional transducers and cMUTs. Conventional transducers require higher excitation voltages (peak to peak greater than 100V) to generate acoustic energy based on the thickness of the ceramic plate. For cMUTs, in addition to applying AC signals, a higher dc bias voltage (greater than 100V) needs to be applied to control the film gap, thereby improving the electromechanical coupling coefficient of the device. Whereas pMUTs requires much lower ac voltages than the two (typically 30V peak-to-peak) to drive the piezoelectric material to transmit acoustic energy and does not require a dc bias voltage. Although both pMUTs and cMUTs may be directly integrated with a control circuit into a miniaturized device, the voltage required for pMUTs is low, which is more advantageous for application to portable equipment for medical ultrasound, and the like. However, the existing pMUTs still need to be further improved in terms of ultrasonic transmission power, ultrasonic reception bandwidth, and the like, so as to improve the resolution and performance of ultrasonic detection.
Disclosure of Invention
In order to overcome the problems in the prior art, the present invention aims to provide a combined thin film pMUTs and a method for preparing the same, so as to improve the feasibility and reliability of the pMUTs chip preparation process and the consistency of the unit structure and performance while increasing the ultrasonic transmission power and the ultrasonic receiving bandwidth.
The invention provides a combined film pMUTs which comprises a multilayer composite film 1 and a substrate structure 2 from top to bottom;
the multilayer composite film 1 is formed by combining a piezoelectric driving layer structure 1-1 and a non-driving layer structure 1-2; the piezoelectric driving layer structure 1-1 consists of a top electrode 1-1-1, a dielectric layer 1-1-2 and a bottom electrode 1-1-3 from top to bottom in the thickness direction; the dielectric layer 1-1-2 is formed by compounding multiple layers of insulating materials;
a circular cavity 3 and an annular cavity 4 are etched on the substrate structure 2, and the annular cavity 4 and the circular cavity 3 are in a concentric position; the circular cavity 3, the annular cavity 4 and the multilayer composite film 1 form a circular film 5 capable of generating bending vibration and an annular film 6 concentric with the circular film;
the top electrode 1-1-1 consists of a circular film driving electrode 1-1-1-1 covered on the upper surface of the circular film 5 and an annular film driving electrode 1-1-1-2 covered on the upper surface of the annular film 6;
exciting a circular film driving electrode 1-1-1-1 and an annular film driving electrode 1-1-1-2 by adopting driving signals which have the same frequency but have phase difference, wherein the range of the phase difference is 0-2 pi; in-plane stress is generated under the inverse piezoelectric effect of the piezoelectric material layer in the dielectric layer 1-1-2 below the coverage area of the circular thin film driving electrode 1-1-1-1 and the annular thin film driving electrode 1-1-2, so that the circular thin film 5 and the annular thin film 6 are warped to generate bending vibration.
Preferably, the dielectric layer is sequentially provided with a shielding layer 1-1-2-1 and a piezoelectric material layer 1-1-2-2 from top to bottom in the thickness direction of 1-1-2.
Preferably, the circular film driving electrode 1-1-1-1 is arranged at the center of the circular film 5 and is concentric with the circular film 5, and the radius of the circular film driving electrode 1-1-1-1 is 0.6 to 0.8 times of the radius of the circular film 5; as a preferred embodiment of the present invention, the annular thin film driving electrode 1-1-1-2 and the annular thin film 6 are in a concentric ring structure, and the width of the annular thin film driving electrode 1-1-1-2 is between 0.4 and 0.7 times the width of the annular thin film 6.
Preferably, the driving signals V respectively loaded on the circular thin film driving electrode 1-1-1-1 and the annular thin film driving electrode 1-1-1-2 1 And V 2 The two types are sinusoidal, the amplitudes of the two types are equal, and the phase difference is pi.
The preparation method of the combined membrane pMUTs comprises the following steps:
step 1: taking a monocrystalline silicon wafer as a substrate structure 2, and etching a circular cavity 3 and an annular cavity 4 on the upper surface of the substrate structure 2 by adopting a Reactive Ion Etching (RIE) technology;
step 2: taking an SOI wafer, taking the top layer silicon of the SOI wafer as a non-driving layer structure 1-2, and bonding the SOI wafer with the upper surface of a substrate structure 2 with a circular cavity 3 and an annular cavity 4 etched by adopting a silicon-silicon direct bonding technology;
and step 3: thinning the SOI wafer bottom layer silicon 7 to a thickness of only 1 to 50 μm left by a Chemical Mechanical Polishing (CMP) technique;
and 4, step 4: removing the residual SOI wafer bottom layer silicon 7 and the buried layer 8 by a Reactive Ion Etching (RIE) technology;
and 5: in order to improve the film deposition quality of the piezoelectric material layer 1-1-2-2 in the step 7, a magnetron sputtering technology is adopted to deposit 10-100nm of piezoelectric material between the bottom electrode 1-1-3 and the non-driving layer structure 1-2 to serve as a piezoelectric material seed layer 9;
step 6: depositing 50-200 nm metal as a bottom electrode 1-1-3 by adopting a magnetron sputtering technology;
and 7: depositing a piezoelectric material with the thickness of 800-1000 nm by adopting a magnetron sputtering technology to serve as a piezoelectric material layer 1-1-2-2;
and 8: deposition of 60nm SiO by Plasma Enhanced Chemical Vapor Deposition (PECVD) technique 2 As a shielding layer 1-1-2-1;
and step 9: sputtering metal electrode layers on the surfaces of the vibration film and the upper electrode insulating layer, and etching to form a circular film driving electrode 1-1-1-1 and an annular film driving electrode 1-1-1-2;
step 10: and etching the lead hole by a dry method for electrically connecting the bottom electrode with the gold wire.
And 5, the piezoelectric material in the step 5 is AlN or ZnO.
The top electrode 1-1-1 and the bottom electrode 1-1-3 are made of Mo.
When the invention is used for the ultrasonic transmitting transducer, the circular film and the annular film are excited by alternating voltage with a certain phase difference to cause the coupling action between the circular film, the fluid medium and the annular film, thereby greatly improving the unit ultrasonic transmitting power; when the ultrasonic broadband receiving device is used for receiving ultrasonic waves, the ultrasonic broadband receiving performance is realized through the resonance frequency deviation of the circular film and the annular film structure in a fluid medium; when ultrasonic waves are incident, the circular film and the annular film vibrate to generate detectable electric signals, and ultrasonic wave receiving is achieved. The invention utilizes the combined film structure, thereby having the performance of wide ultrasonic receiving bandwidth under the condition of realizing pMUTs high ultrasonic output power.
Compared with the prior art, the combined film pMUTs and the preparation method thereof have the technical advantages that:
1) the circular film and the annular film form a combined film structure, and the circular film and the annular film are excited by adopting a driving signal with a certain phase difference to vibrate, so that the mutual coupling between the circular film, the fluid medium and the annular film is enhanced, and the ultrasonic transmitting power of the pMUTs unit is greatly improved.
2) When the phase difference between the driving voltages for exciting the circular film and the annular film is pi, the circular film and the annular film can mutually absorb the flow of fluid medium discharged by opposite directions due to vibration in each vibration period; when the pMUTs units form the array to work, the flow change of the fluid medium near the unit caused by each pMUTs unit can be prevented from inhibiting the ultrasonic emission power of the pMUTs unit adjacent to the unit, so that the mutual interference among the pMUTs units in the array is further inhibited on the basis of enhancing the ultrasonic emission power of the pMUTs units, and the integral ultrasonic emission power of the pMUTs array formed by the pMUTs units is improved.
3) The sizes of the circular film and the annular film are reasonably matched, so that the resonant frequencies of the circular film and the annular film are deviated, and the ultrasonic receiving bandwidth of the pMUTs is widened.
4) The combined film pMUTs has simple preparation process and high process reliability, and the structure and the performance consistency of the chip unit are good.
Description of the drawings:
FIG. 1 is a schematic axial view of the modular membrane pMUTs of the present invention.
FIG. 2 is a top view and a cross-sectional view of a modular membrane pMUTs in accordance with the present invention.
FIG. 3 is a schematic diagram of the combined membrane pMUTs drive signal loading and operating mode of the present invention.
FIG. 4 is a schematic representation of the steps of the method of making modular membrane pMUTs of the present invention.
FIG. 5 is a comparison of the ultrasonic emission sensitivity in water of the modular membrane pMUTs of the present invention and the optimized structure of a conventional circular membrane pMUTs of the same operating frequency.
FIG. 6(a) is a schematic diagram showing the relationship between the membrane mode shape and the flow pattern of a fluid medium in the operating state of the modular membrane pMUTs of the present invention.
FIG. 6(b) is a schematic diagram showing the relationship between the membrane mode shape and the fluid flow pattern of the assembled membrane pMUTs of the present invention in the operating state.
FIG. 7 is a diagram showing the arrangement of cells in a one-dimensional linear array and the numbering of the cells in the array, and the minimum spacing between the cells is 10 μm.
FIG. 8 is a view of the modular membrane pMUTs of the present invention arranged in the array of FIG. 7 and emitting ultrasound in phase; the output power frequency response curves of each pMUTs unit with corresponding numbers and the combined film pMUTs unit of the invention when working independently are compared.
FIG. 9 is a conventional circular membrane pMUTs arranged in the array shown in FIG. 7 and subjected to in-phase ultrasound transmission; the output power frequency response curves of each correspondingly numbered pMUTs unit when operating alone were compared with those of the conventional circular membrane pMUTs unit.
FIG. 10(a) is a schematic diagram of the excitation condition of a two-dimensional rectangular array composed of conventional circular thin film pMUTs units by the same phase excitation signal.
FIG. 10(b) is a schematic diagram of the same phase excitation signal excitation condition of a two-dimensional rectangular array composed of the combined thin-film pMUTs units of the present invention.
Fig. 11 is a comparison of ultrasonic sound pressure at the same location on the axis of the array as a function of excitation signal frequency for the operating mode of fig. 10(a) (b) for an array comprised of conventional pMUTs units and modular membrane pMUTs units according to the present invention.
FIG. 12(a) is a schematic diagram of the phased array operating conditions of a two-dimensional rectangular array composed of conventional circular thin film pMUTs cells.
FIG. 12(b) is a schematic illustration of the phased array operating conditions of a two-dimensional rectangular array of the modular thin film pMUTs elements shown.
FIG. 13(a) is a graph showing the sound pressure distribution along the axial line of the array of conventional circular membrane pMUTs under different operating frequencies under the operating conditions shown in FIG. 12 (a).
Fig. 13(b) shows the sound pressure distribution on the axial line of the array under different operating frequencies under the operating condition shown in fig. 12(b) of the array composed of the combined thin film pMUTs units.
FIG. 14 is a schematic diagram of the principle of the wide receive bandwidth characteristics of ultrasound caused by the deviation of the center resonant frequency of the fluid medium between the circular membrane and the annular membrane in the modular membrane pMUTs unit of the present invention.
Detailed Description
The invention is described in detail below with reference to the accompanying drawings:
the invention provides a combined film pMUTs and a preparation method thereof, aiming at improving the feasibility and the reliability of a pMUTs chip preparation process and the consistency of a unit structure and performance while increasing the transmitting power of the pMUTs and the ultrasonic receiving bandwidth.
As shown in fig. 1, 2 and 3, a combined membrane pMUTs of the present invention is composed of a multi-layered composite membrane 1 and a base structure 2 from top to bottom.
The multilayer composite film 1 is formed by combining a piezoelectric driving layer structure 1-1 and a non-driving layer structure 1-2. The piezoelectric driving layer structure 1-1 is composed of a top electrode 1-1-1, a dielectric layer 1-1-2 and a bottom electrode 1-1-3 from top to bottom in the thickness direction.
The dielectric layer 1-1-2 is formed by compounding multiple layers of insulating materials, and as a preferred embodiment of the invention, the dielectric layer sequentially comprises a shielding layer 1-1-2-1 and a piezoelectric material layer 1-1-2-2 from top to bottom in the thickness direction.
A circular cavity 3 and an annular cavity 4 are etched on the substrate structure 2, and the annular cavity 4 and the circular cavity 3 are in concentric positions. The circular cavity 3, the annular cavity 4 and the multilayer composite film 1 form a circular film 5 which can generate bending vibration and an annular film 6 which is concentric with the circular film.
The top electrode 1-1-1 consists of a circular film driving electrode 1-1-1-1 covered on the upper surface of the circular film 5 and an annular film driving electrode 1-1-1-2 covered on the upper surface of the annular film 6; as a preferred embodiment of the invention, the circular thin film driving electrode 1-1-1-1 is arranged at the central position of the circular thin film 5 and is concentric with the circular thin film 5, and the radius of the circular thin film driving electrode 1-1-1-1 is 0.5 to 0.8 times of the radius size of the circular thin film 5; as the preferred embodiment of the invention, the annular thin film driving electrode 1-1-1-2 and the annular thin film 6 are in a concentric ring structure, and the width of the annular thin film driving electrode 1-1-1-2 is 0.4 to 0.7 times of the width of the annular thin film 6.
Exciting a circular film driving electrode 1-1-1-1 and an annular film driving electrode 1-1-1-2 by adopting driving signals which have the same frequency but have phase difference, wherein the range of the phase difference is 0-2 pi; as a preferred embodiment of the present invention, the driving signals V respectively applied to the circular thin film driving electrode 1-1-1-1 and the annular thin film driving electrode 1-1-1-2 1 And V 2 The two signals are sinusoidal signals, the amplitudes of the two signals are equal, and the phase difference is pi; the in-plane stress is generated under the inverse piezoelectric effect of the piezoelectric material layer 1-1-2-2 below the coverage area of the circular film driving electrode 1-1-1-1 and the annular film driving electrode 1-1-2, so that the circular film 5 and the annular film 5 are formed6 bending vibration is generated by warping;
a method for preparing a combinatorial thin film construct pMUTs, comprising the steps of:
step 1: taking a monocrystalline silicon wafer as a substrate structure 2, and etching a circular cavity 3 and an annular cavity 4 on the upper surface of the substrate structure 2 by adopting a Reactive Ion Etching (RIE) technology;
step 2: taking an SOI wafer, taking the top layer silicon of the SOI wafer as a non-driving layer structure 1-2, and bonding the SOI wafer with the upper surface of a substrate structure 2 with a circular cavity 3 and an annular cavity 4 etched by adopting a silicon-silicon direct bonding technology;
and step 3: thinning the SOI wafer bottom layer silicon 7 to a thickness of only 1 to 50 μm left by a Chemical Mechanical Polishing (CMP) technique;
and 4, step 4: removing the residual SOI wafer bottom layer silicon 7 and the buried layer 8 by a Reactive Ion Etching (RIE) technology;
and 5: in order to improve the film deposition quality of the piezoelectric material layer 1-1-2-2 in the step 7, a magnetron sputtering technology is adopted to deposit 10-100nm of piezoelectric material between the bottom electrode 1-1-3 and the non-driving layer structure 1-2 to serve as a piezoelectric material seed layer 9;
step 6: depositing 50-200 nm metal as a bottom electrode 1-1-3 by adopting a magnetron sputtering technology;
and 7: depositing a piezoelectric material with the thickness of 800-1000 nm by adopting a magnetron sputtering technology to serve as a piezoelectric material layer 1-1-2-2;
and 8: deposition of 60nm SiO by Plasma Enhanced Chemical Vapor Deposition (PECVD) technique 2 As a shielding layer 1-1-2-1;
and step 9: sputtering metal electrode layers on the surfaces of the vibration film and the upper electrode insulating layer, and etching to form a circular film driving electrode 1-1-1-1 and an annular film driving electrode 1-1-1-2;
step 10: and etching the lead hole by a dry method for electrically connecting the bottom electrode with the gold wire.
In this embodiment, the piezoelectric material in step 5 is AlN.
The material of the top electrode 1-1-1 and the bottom electrode 1-1-3 is Mo in this embodiment.
In the embodiment, AlN is used as a preferred embodiment of the piezoelectric material, but does not exclude the feasibility of selecting a plurality of piezoelectric materials such as PZT and ZnO as the piezoelectric material layer 1-1-2-2; the preferred embodiment of Mo as the material of the top electrode 1-1-1 and the bottom electrode 1-1-3 is not excluded, but the feasibility of using various metal materials such as Au, Al, etc. as the material of the top electrode 1-1-1 and the bottom electrode 1-1-3 is not excluded.
The simulation comparison of the ultrasonic emission sensitivity in water is carried out on the traditional circular thin-film structure pMUTs and the combined thin-film type pMUTs which have the same unit resonant frequency of 9.7MHz in water through Comsol Multiphysics simulation software under the condition that the excitation voltage amplitude and the working frequency are the same; as shown in fig. 5, the ultrasound transmission sensitivity of the combined membrane pMUTs is improved by 1500% compared to the optimized structure of the conventional pMUTs unit having only a circular membrane.
When the phase difference between the driving voltages for exciting the circular film and the annular film is pi, the circular film and the annular film can mutually absorb the flow of fluid medium discharged by opposite directions due to vibration in each vibration period; when the pMUTs units form an array to work, the ultrasonic transmitting power of the pMUTs units adjacent to the pMUTs units can be prevented from being inhibited by the flow change of the fluid medium near the units caused by each pMUTs unit, so that the mutual interference among the pMUTs units in the array is further inhibited on the basis of enhancing the ultrasonic transmitting power of the pMUTs units; and the overall ultrasonic emission power of the pMUTs array consisting of the pMUTs units is improved. FIG. 6(a) is a schematic diagram showing the relationship between the vibration mode of the membrane and the flow pattern of the fluid medium in the operating state of the modular membrane pMUTs of the present invention, in which it can be seen that the circular membrane bent downward absorbs the flow of the fluid medium that is removed by the annular membrane bent upward; it can be seen from fig. 6(b) that the downward curved annular membrane absorbs the flow of the fluid medium discharged by the upward curved circular membrane.
The working mechanism is subjected to simulation verification through Commol Multiphysics:
firstly: as shown in fig. 7, a one-dimensional linear array was formed by combining the combined thin-film pMUTs having resonant frequencies of 9.7MHz in water and the conventional pMUTs having only a circular thin film, and ultrasonic emission was performed in phase with each unit, thereby verifying the mutual crosstalk characteristics between the units. As shown in fig. 8, it was found that the frequency response curve of each combined membrane pMUTs unit in the one-dimensional linear array always coincides with the frequency response curve when it is operated alone, and the resonance frequency point does not shift; as shown in fig. 9, in the conventional circular pMUTs unit in the one-dimensional linear array, mutual interference between the units is serious, so that the frequency response curve of each unit in the one-dimensional array is seriously deformed relative to the frequency response curve when the unit is operated alone, and the resonant frequency of the unit in the one-dimensional linear array cannot be accurately obtained.
Secondly, the method comprises the following steps: as shown in fig. 10(a) and 10(b), two-dimensional rectangular arrays having the same area are respectively formed by combined thin-film pMUTs having unit resonant frequencies of 9.7MHz in water and conventional pMUTs having only a circular thin film, and ultrasonic emission is performed by making the units in phase; as shown in fig. 11, finite element simulation was performed on the sound pressure value at a position 0.8mm away from the array on the array axis, and it was found that the sound pressure generated on the array axis by the array composed of the combined thin film pMUTs units is much higher than the sound pressure of the equal-area array composed of the conventional circular pMUTs units, and the maximum sound pressure generated has no difference from the resonance frequency when the array works alone;
and finally: as shown in fig. 12(a) and 12(b), a two-dimensional rectangular array with the same area is formed by the combined thin film pMUTs with the unit resonant frequency of 6.3MHz in water and the conventional pMUTs with only a circular thin film, and the ultrasonic emission phase difference between each column of units in the two-dimensional array is controlled by using a phased array line focusing ultrasonic emission mode; as shown in fig. 13(a) and 13(b), the sound pressure distribution on the central axis of the array was subjected to finite element simulation. It was found that the array composed of the combined membrane pMUTs units generates much higher sound pressure on the array axis than the equal-area array composed of the conventional circular membrane pMUTs units, and the frequency point of the maximum sound pressure generated is the same as the resonance frequency of the single unit when it normally works. When an array consisting of the traditional circular membrane pMUTs units works, the central working frequency of the array cannot be identified, and the complexity of the array design is increased.
As shown in fig. 14, the sizes of the circular membrane and the annular membrane are reasonably matched, so that the resonant frequencies of the circular membrane and the annular membrane are deviated, and the ultrasonic receiving bandwidth of the pMUTs is widened.
The above description is only one embodiment of the present invention, and not all or only one embodiment, and any equivalent alterations to the technical solutions of the present invention, which are made by those skilled in the art through reading the present specification, are covered by the claims of the present invention.
Claims (7)
1. A modular membrane pMUTs, characterized in that: the composite film consists of a plurality of layers of composite films (1) and a substrate structure (2) from top to bottom;
the multilayer composite film (1) is formed by combining a piezoelectric driving layer structure (1-1) and a non-driving layer structure (1-2); the piezoelectric driving layer structure (1-1) is composed of a top electrode (1-1-1), a dielectric layer (1-1-2) and a bottom electrode (1-1-3) from top to bottom in the thickness direction; the dielectric layer (1-1-2) is formed by compounding multiple layers of materials;
a circular cavity (3) and an annular cavity (4) are etched on the substrate structure (2), and the annular cavity (4) and the circular cavity (3) are in a concentric position; the parts of the multilayer composite film (1) above the circular cavity (3) and the annular cavity (4) are respectively a circular film (5) capable of generating bending vibration and an annular film (6) concentric with the circular film;
the top electrode (1-1-1) consists of a circular film driving electrode (1-1-1-1) in a circular film (5) and an annular film driving electrode (1-1-1-2) in an annular film (6);
exciting the circular film driving electrode (1-1-1-1) and the annular film driving electrode (1-1-1-2) by adopting driving signals with the same frequency but phase difference, wherein the range of the phase difference is 0-2 pi; the piezoelectric material layer in the dielectric layer (1-1-2) below the coverage area of the circular film driving electrode (1-1-1) and the annular film driving electrode (1-1-1-2) generates in-plane stress under the action of inverse piezoelectric effect, so that the circular film (5) and the annular film (6) are warped to generate bending vibration.
2. The modular membrane pMUTs of claim 1, wherein: the dielectric layer (1-1-2) is sequentially provided with a shielding layer (1-1-2-1) and a piezoelectric material layer (1-1-2-2) from top to bottom in the thickness direction.
3. The modular membrane pMUTs of claim 1, wherein: the circular film driving electrode (1-1-1-1) is arranged at the center of the circular film (5) and is concentric with the circular film (5), and the radius of the circular film driving electrode (1-1-1-1) is 0.5 to 0.8 times of the radius of the circular film (5); the annular film driving electrode (1-1-1-2) and the annular film (6) are in a concentric ring structure, and the width of the annular film driving electrode (1-1-1-2) is 0.4 to 0.7 times of the width of the annular film (6).
4. The modular membrane pMUTs of claim 1, wherein: a driving signal V loaded on the circular film driving electrode (1-1-1-1) and the annular film driving electrode (1-1-1-2) 1 And V 2 The two signals are sinusoidal signals, and the amplitudes of the two signals are equal, and the phase difference is pi.
5. The method of preparing the modular membrane pMUTs of any one of claims 1 to 4, wherein: the method comprises the following steps:
step 1: taking a monocrystalline silicon wafer as a substrate structure (2), and etching a circular cavity (3) and an annular cavity (4) on the upper surface of the substrate structure (2) by adopting a Reactive Ion Etching (RIE) technology;
step 2: taking an SOI wafer, taking the top layer silicon of the SOI wafer as a non-driving layer structure (1-2), and bonding the SOI wafer with the upper surface of a substrate structure (2) etched with a circular cavity (3) and an annular cavity (4) by adopting a silicon-silicon direct bonding technology;
and 3, step 3: thinning the bottom silicon (7) of the SOI wafer to a thickness of only 1 to 50 μm by a chemical mechanical polishing technique;
and 4, step 4: removing the residual SOI wafer bottom silicon (7) and the buried layer (8) by a reactive ion etching technology;
and 5: in order to improve the film deposition quality of the piezoelectric material layer (1-1-2-2) in the step 7, depositing 10-100nm of piezoelectric material between the bottom electrode (1-1-3) and the non-driving layer structure (1-2) by adopting a magnetron sputtering technology to serve as a piezoelectric material seed layer (9);
step 6: depositing 50-200 nm metal as a bottom electrode (1-1-3) by adopting a magnetron sputtering technology;
and 7: depositing a piezoelectric material with the thickness of 800-1000 nm by adopting a magnetron sputtering technology to serve as a piezoelectric material layer (1-1-2-2);
and 8: depositing 60nm SiO by plasma enhanced chemical vapor deposition 2 As a shielding layer (1-1-2-1);
and step 9: sputtering metal electrode layers on the surfaces of the vibration film and the upper electrode insulating layer, and etching to form a circular film driving electrode (1-1-1-1) and an annular film driving electrode (1-1-1-2);
step 10: and etching the lead hole by a dry method for electrically connecting the bottom electrode with the gold wire.
6. The method of claim 5, wherein: and 5, the piezoelectric material in the step 5 is AlN or ZnO.
7. The method of claim 5, wherein: the top electrode (1-1-1) and the bottom electrode (1-1-3) are made of Mo.
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