Patent Description:
The invention deals with the contactless operation of ultrasonic transducers and ultrasonic transducer arrays. This method addresses both the contactless transfer of energy and information between the transducer(s) and the controlling subsystem. While there are different types of ultrasound transducers, based on different operating principles - from piezoelectric to Capacitive Micromachined Ultrasonic Transducers (CMUTs), they generally require the application of large voltages (i.e. >50V) for their operation. The novel technology previously invented by the inventors allows the fabrication of polymer-based CMUT (polyCMUTs) arrays that can be operated at lower voltages, opening the path towards contactless (no wire) operation. The present application describes methods for their contactless operation, useful for a wide range of applications, from wearable transducers to high-end ultrasound imaging systems.

Ultrasound transducers have a wide range of applications, from non-destructive testing, consumer electronics (e.g. distance measurement and acoustic interfaces for interaction with objects and position detection, haptic interfaces in smartphones and games, etc.), automotive industry (e.g. potential collision detection) to biomedical imaging systems. They have the large advantage of low cost and non-invasive operation, and thus more than <NUM>% of the clinical medical imaging relies on ultrasound imaging techniques, including the newest features, the 3D and real time 3D imaging. Nevertheless, one of the present limitations of the ultrasonic systems is the physical wire connectivity required between the transducer head and the controlling equipment. This limitation impedes for instance the application of ultrasound transducers as effective wearable body sensors and integrated into more general wearable body sensors networks. The roots of such limitation are to be found in the relative large voltages required by the transducer in order to be effectively operated (in air or in a fluid environment): typically, in ultrasound imaging, pulses with amplitudes around 50V are applied to the transducer in order to generate acoustic pulses that propagate into the medium.

The inventors have previously developed a polymer-based manufacturing technology (<CIT>, <CIT> and <CIT> by Gerardo, Rohling and Cretu) that allows the microfabrication of ultrasonic transducers using polymer membranes, reducing as well the required operating voltages. <CIT> relates to a system comprising a cMUT having a telemetric antenna operative to telemetrically transmit an output signal generated by the cMUT in reception mode.

In this context, at least certain embodiments of the present invention focuses on different techniques that enable a truly contactless/wireless operation of polyCMUTs. While wireless power transfer (WPT) techniques have been applied in the past to various sensor types, there are no wireless, passive ultrasonic transducers.

According to an embodiment of the invention, there is provided a method for the contactless operation of polyCMUTs (energy and data transfer) for near-field applications.

According to an embodiment of the invention, there is provided a method for the contactless operation of polyCMUTs (energy and data transfer) for intermediate-field applications.

According to another embodiment of the invention, there is provided a method for the contactless operation of polyCMUTs (energy and data transfer) using alternating current (AC) signals.

According to another embodiment of the invention, there is provided a method for the contactless operation of polyCMUTs (energy and data transfer) using a combination of alternating current (AC) signals and direct current (DC) enabled by an energy storage device (e.g. a battery) located close to the ultrasound transducer.

According to another embodiment of the invention, there is provided a method for the contactless operation of polyCMUTs (energy and data transfer) using a combination of alternating current (AC) signals and direct current (DC) enabled by two independent electrical transformers.

According to another embodiment of the invention, there is provided a method for the contactless operation of polyCMUTs (energy and data transfer) using a combination of alternating current (AC) signals and direct current (DC) enabled by an electrical transformer with an internal electrical tap.

At least one embodiment of the invention specifies the method for the contactless (wireless) operation of polyCMUTs.

According to another embodiment, there is provided a system comprising: a capacitive micromachined ultrasonic transducer (CMUT); a first alternating current voltage source; a first inductor electrically coupled to the first voltage source; and a second inductor electrically coupled to the CMUT, wherein the second inductor is physically electrically decoupled from, and configured to be wirelessly coupled to, the first inductor.

The first inductor and the second inductor may comprise part of a first air-core transformer.

The first inductor and the second inductor may be separated by no more than approximately ten centimeters.

An electrical resonant frequency of the second inductor and the CMUT may be approximately equal to a mechanical resonant frequency of the CMUT, and the first voltage source may be configured to operate at a frequency approximately equal to the electrical or mechanical resonant frequency.

The electrical resonant frequency may be determined as an LC resonant frequency of an inductance of the second inductor and a capacitance between two electrodes of the CMUT.

The system may further comprise: a first antenna electrically coupled to the first inductor; and a second antenna electrically coupled to the second inductor, wherein first and second inductors are wirelessly coupled via the first and second antennas.

The first inductor and the second inductor may be separated by no more than approximately ten meters.

An electrical resonant frequency of the second inductor and the CMUT may be approximately equal to a mechanical resonant frequency of the CMUT, the first voltage source may be configured to operate at a frequency approximately equal to the electrical or mechanical resonant frequency, and an electrical resonant frequency of the first inductor may be approximately equal to the electrical resonant frequency of the second inductor.

The first voltage source may be configured to be operated at a frequency of at least <NUM>.

The system may further comprise an energy storage device electrically coupled in series with the second inductor and the CMUT.

The system may further comprise: a second alternating current voltage source; a third inductor electrically coupled to the second voltage source; a fourth inductor electrically coupled in series to the second inductor, wherein the fourth inductor is physically decoupled from, and positioned to be wirelessly coupled to, the third inductor; and a rectifier electrically coupled to the fourth inductor and to the CMUT.

The second voltage source may be configured to operate at a frequency outside of a coupling frequency band of the CMUT and higher than that of the first voltage source.

The third and fourth inductors may respectively comprise primary and secondary sides of a second air-core transformer.

The system may further comprise: a third antenna electrically coupled to the third inductor; and a fourth antenna electrically coupled to the fourth inductor, wherein third and fourth inductors are wirelessly coupled via the third and fourth antennas.

The system may further comprise a rectifier tapped along the second inductor and electrically coupled to the CMUT.

The system may further comprise a controller communicatively coupled to the first voltage source, wherein the controller comprises a processor and a memory having stored thereon computer program code executable by the processor and that, when executed by the processor, causes the processor to: operate the first voltage source at a frequency at least a decade above a mechanical resonant frequency of the CMUT; while operating the first voltage source at the frequency at least a decade above the mechanical resonant frequency of the CMUT, measure a reflected impedance of the first inductor; and determine from the reflected impedance a coupling coefficient between the first and second inductors.

According to another embodiment, there is provided use of the system of any of the embodiments described above or suitable combinations thereof for obtaining medical information from a patient, wherein the CMUT comprises a polymer-based capacitive micromachined ultrasonic transducer attached to skin of the patient.

According to another embodiment, there is provided use of the system of any of the embodiments described above or suitable combinations thereof for monitoring structural integrity of a pipe, wherein the CMUT comprises a polymer-based capacitive micromachined ultrasonic transducer attached to the pipe.

According to another embodiment, there is provided use of the system of any of the embodiments described above or suitable combinations thereof for obtaining medical information from a patient, wherein the CMUT comprises a polymer-based capacitive micromachined ultrasonic implanted inside the patient.

According to another embodiment, there is provided use of the system of any of the embodiments described above or suitable combinations thereof for monitoring structural integrity of wings of a plane, wherein the CMUT comprises a polymer-based capacitive micromachined ultrasonic transducer attached to the wings.

According to another embodiment, there is provided a method comprising: applying a first alternating current voltage source across a first inductor; wirelessly transferring power from the first alternating current voltage source to a second inductor; and using the wirelessly transferred power to oscillate a capacitive micromachined ultrasonic transducer (CMUT).

The method may further comprise: receiving an echo at the CMUT, wherein the echo results in a current change in the second inductor wirelessly transferring a signal resulting from the current change from the second inductor to the first inductor; and measuring the signal that has been wirelessly transferred.

An electrical resonant frequency of the second inductor and the CMUT may be approximately equal to a mechanical resonant frequency of the CMUT, and the first voltage source may be operated at a frequency approximately equal to the electrical or mechanical resonant frequency.

The power may be wirelessly transferred using a first antenna electrically coupled to the first inductor and a second antenna electrically coupled to the second inductor.

An electrical resonant frequency of the second inductor and the CMUT may be approximately equal to a mechanical resonant frequency of the CMUT, the first voltage source may be operated at a frequency approximately equal to the electrical or mechanical resonant frequency, and an electrical resonant frequency of the first inductor may be approximately equal to the electrical resonant frequency of the second inductor.

The first voltage source may be operated at a frequency of at least <NUM>.

The method may further comprise applying a direct current bias to the CMUT using an energy storage device electrically coupled in series with the secondary side inductor and the CMUT.

The method may further comprise: applying a second alternating current voltage source across a third inductor; wirelessly transferring power from the second alternating current voltage source to a fourth inductor; rectifying the power that is wirelessly transferred from the second alternating current voltage source to the fourth inductor; and using the power that is rectified to apply a direct current bias to the CMUT.

The second voltage source may be operated at a frequency outside of a coupling frequency band of the CMUT and higher than that of the first voltage source.

The power from the second alternating current voltage source to the fourth inductor may be wirelessly transferred using a third antenna electrically coupled to the third inductor and a fourth antenna electrically coupled to the fourth inductor.

The method may further comprise: tapping power from the second inductor; rectifying the power tapped from the second inductor; and using the power that is rectified to apply a direct current bias to the CMUT.

The method may further comprise: operating the first voltage source at a frequency at least a decade above a mechanical resonant frequency of the CMUT; while operating the first voltage source at the frequency at least a decade above the mechanical resonant frequency of the CMUT, measuring a reflected impedance of the first inductor; and determining from the reflected impedance a coupling coefficient between the first and second inductors.

Features and advantages of the subject matter hereof will become more apparent in light of the following detailed description of selected embodiments, as illustrated in the accompanying figures. As will be realized, the subject matter disclosed and claimed is capable of modifications in various respects, all without departing from the scope of the claims. Accordingly, the drawings and the description are to be regarded as illustrative in nature, and not as restrictive and the full scope of the subject matter is set forth in the claims.

Further features and advantages of the present disclosure will become apparent from the following detailed description, taken in combination with the appended drawings. <FIG> and the corresponding descriptions do not form part of the invention, but are suitable to explain the invention.

The term "Capacitive Micromachined Ultrasonic Transducers" (CMUT) is intended to mean an ultrasonic device consisting of an electrically conductive membrane suspended above a cavity. The fabrication materials for CMUTs can be, but are not limited to: silicon, polysilicon, silicon nitride, silicon dioxide.

"The term "Polymer-based Capacitive Micromachined Ultrasonic Transducer" (polyCMUT) is intended to mean a layered ultrasonic device with polymeric membrane containing an embedded upper electrode suspended above a cavity. Examples of a polyCMUT are found in US Patents <CIT>, <CIT> and <CIT>. For clarity, polyCMUTs are considered an example of CMUTs, where polyCMUTs have a top electrode embedded (sandwiched) between two polymer layers to form the membrane, while CMUTs have the top electrode typically above the membrane.

"Substrate" means an underlying substance or layer upon which the polyCMUTs devices are fabricated. Substrates can comprise a range of metallic (e.g. Aluminum), non-metallic (e.g. ceramics, composite materials), semiconductors (e.g. silicon) and even polymer-based materials such as polyimide. A substrate can also comprise optically transparent or semi-transparent materials such as glass or Indium Tin Oxide (ITO). A substrate can be rigid, semi-rigid or flexible. A substrate can also comprise combinations of the aforementioned options, for example, a piece of glass covered by a layer of Indium Tin Oxide, or a piece of polyimide covered by a metallic layer.

As used herein, "array" is intended to mean a group of polyCMUT elements aligned side by side in a one-dimensional (1D) arrangement, multiple linear arrays located side by side (<NUM>. 5D) or two-dimensional array (2D array, often called matrix array) of polyCMUT elements in communication with each other and capable of communication (once connected or active) with user interfaces either by wired communication or wireless signals.

As used herein, "contactless" or "wireless" is intended to mean a form of coupling or communication that does not require physical wires. This coupling can be obtained by inductive coupling using a pair of inductors in air or any other media. The coupling can also be obtained by radio frequency (RF) means using antennas or an array of antennas.

As used herein, "field" refers to a space or range within which two or more objects or devices can be reached or can be identified from a particular viewpoint or through a piece of apparatus (such as an antenna).

As used herein, "electrical model" or "model" refers to the representation in the form of electrical components and circuits of systems. These systems can be either in the electrical, the mechanical or acoustic domain and can be represented by standard electrical components.

In this disclosure, the word "comprising" is used in a non-limiting sense to mean that items following the word are included, but items not specifically mentioned are not excluded. It will be understood that in embodiments which comprise or may comprise a specified feature or variable or parameter, alternative embodiments may consist, or consist essentially of such features, or variables or parameters. A reference to an element by the indefinite article "a" does not exclude the possibility that more than one of the elements is present, unless the context clearly requires that there be one and only one of the elements.

In this disclosure the recitation of numerical ranges by endpoints includes all numbers subsumed within that range including all whole numbers, all integers and all fractional intermediates (e.g., <NUM> to <NUM> includes <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, and <NUM> etc.). In this disclosure the singular forms an "an", and "the" include plural referents unless the content clearly dictates otherwise. Thus, for example, reference to a device containing "a system" includes a combination of two or more system.

In this disclosure the term "or" is generally employed in its sense including "and/or" unless the content clearly dictates otherwise.

In this disclosure a first value being "approximately" equivalent to a second value means the first value is within <NUM>% of the second value unless otherwise indicated or the context otherwise requires.

The invention addresses various ways for the contactless operation of ultrasonic transducers, for near-field and intermediate-field operation. It solves the problem of the wireless power transfer (to be converted into the acoustic energy necessary for the ultrasonic interrogation pulses) and of the contactless reading the information provided by the incoming ultrasound signals (from scattered echoes or generated through specific phenomena, like in the case of the photo-acoustic effect). At least some embodiments of the invention addresses several aspects related to the optimum contactless operation in innovative ways:.

At least some embodiments of the invention addresses various modalities for contactless interfacing fully-passive and semi-passive (embedding a DC battery) CMUT arrays with the controller system responsible for its configuration, activation, readout and data processing.

Different techniques can be used depending on the relative distance between the ultrasound transducer and the controller module:
Near-field communication is dedicated to wireless power transfer and communication over short distances (~ <NUM> centimeters range), in which an inductive coupling is mostly sufficient.

Intermediate-field communication (centimeter to meters range) is contactless resonant coupling that can extend the communication range between the ultrasonic transducer and the master equipment.

The direct impact of contactless ultrasonic transducers will reflect in a wide range of applications. At the high-end level, the present ultrasound imaging equipment has standardized (costly) cable interfaces for simultaneous operation on <NUM>, <NUM> or <NUM> channels. When the number of channels significantly increases, like in the case of 3D imaging, analog multiplexing circuit techniques are used in order to avoid the high increase in the number of connecting wires. The wireless coupling between the transducer head and the data acquisition and processing equipment will enable a much larger configuration flexibility, and an easy, non-obstructed manipulation of the transducer head by the operator.

Referring now to the drawings, and more particularly to <FIG>, which illustrates a wireless monitoring patient system composed of one monitoring station <NUM>. Each monitoring station has a local controller <NUM> installed and can accommodate a patient <NUM> with a wireless polyCMUT system ("patch" ultrasound) <NUM>. In this case, the polyCMUT system <NUM> monitors the cardiac vital signs of a patient <NUM>. These systems are operating in a near-field or in an intermediate-field scheme. Control signals and (optional) power signals <NUM> are sent and received wirelessly between the polyCMUT system <NUM> and the controller unit <NUM>. The entire system is managed by a centralized processing unit <NUM>. The signals coming from the controller unit <NUM> are received by a connecting cable (not shown) or wirelessly (not shown) and processed in internally by a computer <NUM>. Finally, the information of the monitored patient or patients is displayed on a monitor <NUM> or sent to a remote monitoring station (not shown). This exemplification highlights some of the benefits of these wireless systems, such as an unobstructed monitoring system (especially useful in intensive care units), a reduced need for electronic and software, the ability to monitor several patients at the same time, among other benefits.

Referring now to <FIG>, a different category of application relates to wearable ultrasound transducers, attached to the body of patients in the form of small or large patches. The contactless activation and readout of the acoustic echo signals is an essential component of such a system. The "patch" ultrasound <NUM> can be fabricated on a substrate <NUM> which can be either rigid, semi-rigid or flexible. A polyCMUT array <NUM> is fabricated on the substrate <NUM> and can be a linear array (1D) or a matrix array (2D). Several electronic components <NUM> are needed for the proper operation of polyCMUTs, such as (but not limited to) beamforming circuits, analog-to-digital converters, microcontrollers, voltage pulsers, multiplexers, etc. An optional energy storage device <NUM> (such as a battery) can also be part of the system. A wireless antenna <NUM> is used to send and receive signals to and from a controller (not shown). The ultrasound patch <NUM> is adhesively fixed on the body <NUM> for the imaging of a certain area (e.g. heart or lungs), and operated from an electronic device <NUM> (such as a tablet or smartphone) that can provide the necessary energy for both the transmission of the acoustic signals and the wireless collection of data. The information collected from the polyCMUT is internally processed and displayed either in a display <NUM> or simply displayed as text information <NUM>.

The operation of the CMUT transducer -or more generally of microelectromechanical systems (MEMS) resonator- can be described in terms of the energy flow between the electric and the acoustic domains.

The sketch of a basic CMUT transducer cell structure is illustrated in <FIG>. The cross-section of a basic CMUT <NUM> structure shown. It consists of a substrate <NUM>, a fixed electrode <NUM> integrated on the substrate <NUM>, supporting walls <NUM> and a second electrode associated with a flexible thin membrane <NUM>. The thin membrane can be itself conductive, or otherwise a conductive electrode is deposited on the top of it or embedded within the membrane (as in United States Patent Nos. <CIT>, <CIT> and <CIT>).

<FIG> shows the operation of CMUTs in transmit mode (Tx). The bottom <NUM> and top electrodes <NUM> are connected to a voltage source comprised of an AC voltage source <NUM> and an optional DC voltage source <NUM> which induces an electrical current <NUM>. This electrical current <NUM> induces an electrostatic force between the electrodes and causes the metalized membrane <NUM> until a deformation <NUM> is obtained. The oscillating vibration of the membrane <NUM> induced by the oscillating current <NUM> creates ultrasound waves <NUM> that propagates in a medium (not shown) following a direction <NUM>. <FIG> shows a CMUT in receive mode (Rx). The echoes <NUM> received from reflection surfaces or from scatterers from a certain direction <NUM> will deform (through the exerted acoustic pressure) the membrane <NUM>. This deformation will change the equivalent electrical capacitance, that can be detected in the electrical domain through the detected current change <NUM>. The operation assumes the application of a DC+AC voltage source - the pre-bias given by the DC voltage source <NUM> modulates the sensitivity of the transducer and ensures a linearization of its operation, while the AC voltage source <NUM> actuates the membrane (in packages of pulses or in continuous mode), typically at its mechanical resonance frequency, in order to ensure an optimum electromechanical energy transfer coupling.

Referring now to <FIG>, assuming a simplified one degree of freedom model for the displacement of the membrane <NUM>, a reduced order macro-model, based on charge and power conservation principles, useful for explaining the power transfer aspects, is illustrated in <FIG>, based on a generalized across-through modeling approach [<NUM>] that combines the acoustic domain <NUM> and mechanical domain <NUM> into a single electrical representation. The equivalent nonlinear capacitor Ce <NUM> models the electrical capacitance between the two electrodes. The nonlinear electrical resistor Re <NUM> models the electrical power transfer into the mechanical domain <NUM>. The physical circuit representation in the mechanical domain is based on the power conjugate variables force and velocity, with force as through variable (generalized current) and velocity as across variable (generalized voltage). The electro-mechanical coupling is represented by the nonlinear force controlled source Fe <NUM>; the capacitance Cm <NUM> represents the effective inertial mass for the corresponding vibration mode, while the inductor Lm <NUM> models the equivalent spring constant of the CMUT membrane <NUM>. The resistor Rm <NUM> characterizes the damping of the membrane during its vibration, while the complex impedance Zac <NUM> represents the equivalent acoustic interaction with the acoustic impedance from the medium. For the back reflected echoes, equivalent acoustic generated forces will be mapped to an external force sources (not shown).

Referring now to <FIG>, from the physical network representation perspective, the entire dynamic behavior at the electrical port can be characterized by an equivalent (time-varying) Thevenin circuit <NUM> using an equivalent impedance <NUM> and an equivalent voltage source <NUM>. Referring now to <FIG>. The circuit can also be represented as a Norton equivalent circuit <NUM> using an equivalent impedance <NUM> and an equivalent current source <NUM>.

One of the key aspects is that, monitoring only the electrical across/through variables at the electrical port (voltage and current) will provide the necessary information about the relevant processes happening in the acoustic domain. The electrical impedance Zeq <NUM> will have a capacitive dominated behavior, but with a back reflection of the mechanical resonant behavior that can be detected in the electrical domain. The macromodel circuit <NUM> is nonlinear and valid for a general large signal operation, being able to predict strongly nonlinear phenomena like electrostatic spring softening and driving the membrane into pull-in or collapse mode (loss of stability border). Nevertheless, for small mechanical vibration amplitudes, it can be linearized around the DC operating point, leading to a linear time invariant equivalent circuit where a gyrator ensures the coupling between the electrical <NUM> and the mechanical domains <NUM>. The typical energy conversion efficiency for the electro-acoustic coupling is around <NUM>% and depends on the DC operating point determined by the applied DC-bias voltage.

A first example is shown in <FIG>, where there is a circuit diagram of a contactless polyCMUT system that operates only in AC <NUM>. The circuit <NUM> describes the case of the inductive coupling for near-field contactless interface. It has an AC voltage source <NUM> with a frequency ω<NUM> (not shown) that supplies an electrical current Ig <NUM> to an air-core transformer <NUM> with a coupling coefficient Kair <NUM>. The air-core transformer <NUM> comprises a first inductor on the transformer's <NUM> primary side that is inductively coupled to a secondary inductor on the transformer's <NUM> secondary side; the inductors are physically electrically decoupled from each other. The CMUT element in the form of a Thevenin circuit <NUM> can be coupled to the electrical domain with the help of two magnetically coupled inductors (transformer <NUM>), one on the master controller side, and the other connected to the CMUT element <NUM>.

In this wireless connection there are two main frequencies. The first one is the electrical LC resonant frequency ωe derived from the combination of the inductor on the secondary side of the transformer <NUM> and the electrical capacitance form the CMUT <NUM>. The second frequency is the mechanical frequency at which the CMUT membrane resonates (its natural vibration frequency in a medium) ωmech (not shown, but discussed in more detail in respect of <FIG> below). It is important to note that a matching between the electrical frequency ωe and the mechanical frequency ωmech is desired for an optimum electromagnetic energy coupling, translating into an increased electromechanical efficiency of the overall system.

The master controller (left portion of circuit <NUM>) provides, in this alternative, through the air-coupled inductors <NUM>, the voltage Vg <NUM>, necessary for the CMUT to operate with optimum efficiency (at its mechanical resonance frequency). In the same time, the controller monitors the value of the current Ig <NUM>, so that it can estimate, at any given moment, the reflected input equivalent circuit (e.g. Thevenin <NUM> or Norton equivalent <NUM> port circuit) seen from the primary transformer side, as a readout mechanism. The normal transmit /receive cycle can be similar with the wired operation: a burst of several harmonic periods is transmitted by Vg <NUM>, followed by monitoring the echo responses, reflected in the equivalent Thevenin/Norton parameters.

Referring now to <FIG>, One of the main challenges with this scheme is that the inductive coupling coefficient will depend on the distance and orientation between the two inductors, making the readout of the echo pulses difficult to calibrate in amplitude. A way of compensating this, with the price of an increased circuit complexity, is to use a calibration circuit <NUM> with a more complex actuation signal voltage source <NUM>, including a calibration capacitor <NUM>. In normal transmit mode, the voltage source <NUM> contains a package of several harmonic periods with a frequency tuned for the optimum electromechanical energy transfer (the mechanical resonance frequency). When a calibration is desired, in order to identify the in-air magnetic coupling coefficient Kair <NUM>, a package of harmonic periods will be sent though the current <NUM>, at a frequency much higher than the mechanical resonant frequency (e.g., at least one decade higher), so that the membrane will not vibrate; as a result, a constant and known capacitance value <NUM> will be reflected into the primary port of the transformer, depending on Kair value. In at least some embodiments, instead of sending a package of harmonic periods, calibration may be performed by operating the voltage source <NUM> to generate any suitable waveform (e.g., a sinusoid) at a frequency at least one decade higher or at least one decade lower than the mechanical resonant frequency.

The calibration (determination of Kair) is then performed by monitoring the current Ig <NUM> and indirectly measuring the reflected impedance on the controller side. The inductive coupling method for the transmit and receive operation of CMUT transducers <NUM> is relatively simple to implement, but it only allows the AC coupling in the circuit presented - it is not possible to apply a direct DC-bias on the CMUT transducer for an optimized operation.

A second example is shown in <FIG>. It is shown a circuit for the contactless operation of CMUTs with DC abilities <NUM>. A separate energy storage device <NUM> (e.g. DC battery) can be included together with the CMUT element on the secondary side of the circuit, responsible for the DC-bias, but this will only ensure a limited operating time since the energy storage device <NUM> will discharge over time. In <FIG>, the mechanical resonant frequency is defined by the resonant frequency of the circuit comprising the combination of Cm, Lm, Rm, and Zac. Practically, Zac may in some situations have no appreciable capacitance (e.g., when the CMUT is emitting an acoustic signal into the air). In other examples, the capacitance of Zac may be relevant (e.g., when the CMUT is emitting an acoustic signal into a liquid).

Another example is shown in <FIG>. A better alternative is to use the same inductive coupling principle with a circuit that has two separate voltage sources <NUM> and <NUM>. A first voltage source <NUM> with a frequency ω<NUM> will be responsible for the actuation of the CMUT (in the usual packages of sine waves), while a second voltage source <NUM> with a frequency ω<NUM> is used to provide the DC-bias voltage. The first voltage source <NUM> has the frequency ω<NUM> tuned for the efficient actuation of the CMUT transducer though a first transformer <NUM>, while the second voltage source <NUM> may have the frequency ω<NUM> set outside of the CMUT coupling frequency band though the second transformer <NUM>. The first transformer <NUM> comprises the first and second inductors as described above, while the second transformer <NUM> comprises a third inductor on its primary side and a fourth inductor on its secondary side. In at least some embodiments, the frequency ω<NUM> is also higher than the frequency ω<NUM>. The second voltage source <NUM> will not contribute to the actuation of the CMUT (and therefore will not generate any acoustic signals). A rectification circuit ("rectifier") <NUM> located on the secondary side of the circuit and interfacing with the second transformer <NUM> will provide a DC voltage for the operation of CMUTS. This rectifier <NUM> could be made from passive components only.

Another example of the invention is shown in <FIG>. A second way of achieving both AC actuation and DC biasing uses a single AC voltage source <NUM> on the controller side, together with a center tap transformer <NUM> and a rectifier circuit <NUM> on the secondary side. The position of the tap in the secondary inductance (secondary side of transformer <NUM>) will dictate the ratio between the DC-bias and the AC actuation voltage. This tap transformer could be fixed or could have a variable tap for an adjustment of the desired DC bias level for the CMUT circuit <NUM>.

Another embodiment of the invention is shown in <FIG>. A more efficient power transmission technique, able to deal with intermediate-field power transfer over a couple of meters distance, relies on concentrating the energy transfer in a narrow spectral band through a resonant coupling. In such a case both the side with the voltage source <NUM> ("master side") and the side with the membrane ("membrane side") comprise matched resonant circuits (e.g., the voltage source <NUM> operates at the resonant frequency defined by the capacitance <NUM> and inductance of the first inductor <NUM>, which is equivalent to the electrical resonant frequency on the membrane side of the circuit, which is based at least in part on the inductance of the second inductor <NUM>, and the mechanical resonant frequency of the transducer). <FIG> shows a capacitor <NUM> that affects the resonant frequency on the voltage source side of the circuit, which comprises the first inductor <NUM>. This capacitor <NUM> may comprise, for example, a tuning capacitor and/or, depending on the frequency used (e.g., when the frequency is at least <NUM>), the internal (parasitic) capacitance of the first inductor <NUM>. Regardless, the capacitor <NUM> can be used to define the equivalent electrical inductance-capacitance resonance. On the membrane side of the circuit, the equivalent electrical capacitance of the CMUT will contribute to the electrical resonance. An optimum electroacoustic energy transfer will happen when the electrical resonance frequency ωe (not shown) used in the resonant power transfer matches the mechanical resonance ωmech (not shown) of the vibrating membrane (captured by the circuit <NUM>). A first antenna <NUM> is electrically coupled to the first inductor <NUM> and a second antenna <NUM> is electrically coupled to the second inductor <NUM> on the membrane side of the circuit. As with the near-field configurations described above, the second inductor <NUM> is physically electrically decoupled from the first inductor <NUM> (i.e., it is not connected via a physical conductor such as a wire), and is configured to be wireless coupled to the first inductor <NUM>. In contrast to the near-field configurations above, the second inductor <NUM> is configured to be wirelessly coupled to the first inductor <NUM> via the antennas <NUM>, <NUM>. In <FIG> and more generally when intermediate-field coupling is dominant, wireless coupling between the inductors <NUM>, <NUM> occurs via the antennas <NUM>, <NUM> as opposed to directly between the first and second inductors when those inductors comprise part of the air-core transformer <NUM> as described in respect of near-field coupling, above.

The increased complexity and the much narrower coupling bandwidth are compensated by larger power transfer distances, in the meters range. The same principles as before apply, <FIG> shows the scheme for a simple AC-only actuation and readout scheme.

Another embodiment of the invention is shown in <FIG>. It is shown an intermediate-field wireless coupling of CMUTs leveraging the parasitic capacitance represented by capacitor <NUM>. Similar to the case described for <FIG>, there is an energy storage device <NUM> on the membrane side that is electrically coupled to the second inductor <NUM> that provides a DC voltage for the actuation of CMUTs.

Other embodiments of the invention are shown in <FIG> and in <FIG>. <FIG> shows a contactless intermediate-field coupling of CMUTs analogous to the near-field configuration of <FIG>, except the antennas <NUM>, <NUM> are used to facilitate intermediate-field wireless coupling as opposed to via the air-core transformer <NUM> of <FIG>. More particularly, in <FIG> two pairs of coils are used: a first pair comprising the first and the second inductors <NUM>, <NUM> and a second pair comprising the second and the third inductors <NUM>, <NUM>. As in <FIG>, the first and the second antennas <NUM>, <NUM> facilitate intermediate-field wireless coupling between the first and the second inductors <NUM>, <NUM>; analogously, a third antenna <NUM> electrically coupled to the third inductor <NUM> and a fourth antenna <NUM> electrically coupled to the fourth inductor <NUM> facilitate intermediate-field wireless coupling between the third and the fourth inductors <NUM>, <NUM>. <FIG> shows an intermediate-field wireless coupling configuration analogous to the near-field configuration of <FIG>, with the intermediate-field coupling being facilitated by the antennas <NUM>, <NUM> as opposed to via the air-core transformer <NUM> of <FIG>. In these intermediate-field implementations, capacitors <NUM>, <NUM> and <NUM> are used to calibrate the operational transmission frequency of the wireless system, with capacitors <NUM> and <NUM> comprising the parasitic capacitances of the inductors <NUM>, <NUM> when the operating frequency is sufficiently high. In the intermediate-field configurations of <FIG>, the voltage source <NUM> may be operated at a frequency sufficiently high, such as at least <NUM>, to facilitate efficient intermediate-field coupling using the antennas <NUM>, <NUM>, <NUM>, <NUM>.

Referring now to <FIG>, there is shown the physical implementation of the circuit shown in <FIG>. On the electrical source side (left) it is shown the source inductor <NUM> and source capacitor <NUM> magnetically coupled to the transmission inductor <NUM> and transmission capacitor <NUM> through the magnetic flux <NUM>. On the load side (right side) it is shown the load inductor <NUM> and load capacitor <NUM> magnetically coupled to the receiving inductor <NUM> and receiving capacitor <NUM> through the magnetic flux <NUM>. In this case, the group of coils <NUM>, <NUM>, <NUM> and <NUM> essentially forms the air-core transformer <NUM> depicted in <FIG>. To maximize the voltage on the receiving side <NUM>, the source inductor <NUM> and the source capacitor <NUM> are connected in parallel.

Referring now to <FIG>, there is shown the physical assembly of inductors <NUM>, <NUM>, <NUM> and <NUM> from <FIG>. A ferrite core was used on the transmit side to increase the amount of magnetic flux produced, therefore, increasing the operational range (physical separation) between the source inductors (<NUM>, <NUM>) and the load inductors (<NUM>, <NUM>).

Referring now to <FIG>, there is shown an assembled circuit from <FIG>. A function generator is used as the voltage source <NUM>. The prototyping board on the left is used to assemble the transmit circuit using the source and transmission inductors and capacitors <NUM>, <NUM>, <NUM>, <NUM>. The prototyping board on the right is used to assemble the receiving circuit using the load and receiving inductors and capacitors <NUM>, <NUM>, <NUM>, <NUM>. The receiving circuit is connected to a polyCMUT array <NUM> using copper wires. The voltage on the receiving side <NUM> is measured using a laboratory oscilloscope.

Referring now to <FIG>, there is shown the electromechanical measurement setup for the circuit shown in <FIG>. The transmission inductors and capacitors <NUM>, <NUM>, <NUM> and <NUM> are connected to a function generator (not shown) to wirelessly induce a voltage on the receiving inductors and capacitors <NUM>, <NUM>, <NUM> and <NUM>. The induced voltage on the transmission side <NUM> powers a polyCMUT linear array <NUM> located under the microscope lens of a Laser Doppler Vibrometer system MSA-<NUM> (Polytec, CA, USA).

Referring now to <FIG>, there is shown a screenshot of the Laser Doppler Vibrometer software. It is capable of generating a deflection shape of the polyCMUT membrane <NUM> automatically using a set of lasers and optical decoders (not shown). The frequency response <NUM> of the polyCMUT membrane shows a resonant peak at <NUM> when operating in air. For clarity purposes, the polyCMUT membranes from the array <NUM> are electrostatically actuated by a voltage wirelessly induced by an air-core transformer <NUM>.

Certain embodiments of the present invention will be more readily understood by referring to the following examples which are given to illustrate the invention rather than to limit its scope.

In a contactless polyCMUT sensor array mounted on several patients inside a hospital or clinic room, each polyCMUT system obtains vital signs from each patient, for example, blood pressure and ejection fraction of the heart, and optionally images from the inside of the patient. Each of the patients has a polyCMUT-based system associated with his body that communicates wirelessly with a controller and then with a central unit that is capable of controlling several polyCMUT patches at a time. This central unit redirects the gathered information to a local or a remote control station. A technician or a nurse is able to monitor the information from several patients at the same time, and an automatic alert system is part of the monitoring for critical vital signs. The polyCMUT sensor array, controller and central unit keep patients safe, increase efficiency of staff, and reduce the overall electrical, electronic and software requirements for the wireless monitoring of several patients.

A set of contactless polyCMUT arrays is permanently installed in pipes to monitor their structural integrity and detect cracks. An operator or a technician can use a wireless controller to "interrogate" the sensor and assess the structural state of the pipe. A wireless antenna could also be coupled to the polyCMUT array that can be then send and receive signals remotely.

A miniature wireless polyCMUT sensor is implanted inside the body of a person for a constant real-time monitoring. For example, information on the bladder, heart or other organs are monitored without the person being encumbered by wires. This implanted device is then wirelessly coupled to an electronic readout system (for example a smartphone) using inductive coupling. The communication protocol is initiated manually by the implanted person, or automatically, or even remotely.

A wireless polyCMUTs array system is installed (either internally or mounted externally) on the wings of a plane to assess the structural integrity of a wing during flight. The wireless nature of the polyCMUTs ensures a negligible weight is added to the aircraft wings and requires a minimal communication system. The wireless polyCMUT systems can be either interrogated locally from the plane cockpit or remotely from a controlling base station on ground.

Referring now to <FIG>, there is shown the schematic diagram for a Simulation Program with Integrated Circuit Emphasis (SPICE) simulation of the circuit shown in <FIG>. The set of inductors on the primary and secondary side (<NUM>, <NUM>, <NUM>, <NUM>) sharing an air-core is implemented as a transformer with multiple windings. The source capacitor <NUM> and transmission capacitor <NUM> are connected on the primary side, and the load capacitor <NUM> and receiving capacitor <NUM> are connected on the secondary side. Using this configuration, the source voltage <NUM> is used to wirelessly induce a voltage <NUM> on the secondary side that drives the reduced order macro-model of a CMUT element <NUM>, where Vq represents the velocity of the vibrating membrane.

Referring now to <FIG>, there is shown the frequency response from the circuit in <FIG>. The SPICE modeler Multisim™ (National Instruments, Texas, USA) was used for this analysis. A frequency sweep of the input voltage induces a displacement of the membrane measured though the voltage Vq (from <FIG>). The resonant peak is located at <NUM> and matches closely to the frequency response <NUM> obtained experimentally from Figure <NUM>.

It is contemplated that any part of any aspect or embodiment discussed in this specification can be implemented or combined with any part of any other aspect or embodiment discussed in this specification.

Claim 1:
A system comprising:
(a) a capacitive micromachined ultrasonic transducer CMUT (<NUM>);
(b) a first alternating current voltage source (<NUM>);
(c) a first inductor electrically coupled to the first voltage source (<NUM>);
(d) a second inductor (<NUM>) electrically coupled to the CMUT (<NUM>), wherein the second inductor (<NUM>) is physically electrically decoupled from, and configured to be wirelessly coupled to, the first inductor (<NUM>);
(e) a first antenna (<NUM>) electrically coupled to the first inductor (<NUM>); and (f) a second antenna (<NUM>);
the system characterized in that
the second antenna (<NUM>) is electrically coupled to the second inductor (<NUM>), wherein first and second inductors (<NUM>, <NUM>) are wirelessly coupled via the first and second antennas (<NUM>, <NUM>).