This thesis describes the design and realization of integrated ultrasound transceivers for carotid artery imaging and intracardiac echocardiography (ICE). The goal of this work is to investigate system- and circuit-level techniques to address requirements and implementation bottlenecks in these applications. Prototype chips are presented to demonstrate the effective of these techniques. The first prototype provides cable-count reduction and the capability to interface with a large-aperture transducer array for 3D carotid artery imaging. The second prototype is targeted at a 2D ICE probe, and features a novel bipolar high-voltage (HV) pulser, and an analog front-end with continuous time-gain compensation while achieving a superior noise efficiency factor.@en

This article presents an application-specific integrated circuit (ASIC) designed for intra-vascular ultrasound imaging that interfaces 64 piezoelectric transducer elements to an imaging system using a single micro-coaxial cable. Thus, it allows a single-element transducer to be replaced by a transducer array to enable 3-D imaging. The 1.5-mm-diameter ASIC is intended to be mounted at the tip of a catheter, directly integrated with a 2-D array of piezoelectric transducer elements. For each of these elements, the ASIC contains a high-voltage (HV) switch, allowing the elements to transmit an acoustic wave in response to an HV pulse generated by the imaging system. A low-noise amplifier then amplifies the resulting echo signals and relays them as a signal current to the imaging system, while the same cable provides a 3-V supply. Element selection and other settings can be programmed by modulating configuration data on the supply, thus enabling full synthetic aperture imaging. An integrated element test mode measures the element capacitance to detect bad connections to the transducer elements. The ASIC has been fabricated in a 0.18- μm HV CMOS technology and consumes only 6 mW in receive. Electrical measurements show correct switching of 30-V transmit pulses and a receive amplification with a 71-dB dynamic range, including 12 dB of programmable gain over a 3-dB bandwidth of 21 MHz. The functionality of the ASIC has been successfully demonstrated in a 3-D imaging experiment.

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This article presents a readout integrated circuit (ROIC) for capacitive touch-screen panels (TSPs) employing an amplitude-modulated multiple-frequency excitation (AM-MFE) technique. To prevent charge overflow, which occurs periodically at the beat frequency of the excitation frequencies, the ROIC modulates the amplitude of the excitation voltages at a mixing frequency derived from the excitation frequencies. Thus, the ROIC can sense the charge signal without charge overflow and maximize the signal-to-noise ratio (SNR) by increasing the amplitude of the excitation voltages up to the sensing range of the readout circuit. The proposed ROIC was fabricated in a 0.13- $\mu \text{m}$ standard CMOS process and was measured with a 32-in 104 $\times $ 64 touch-screen panel using 1 and 10 mm metal pillars. It reduces charge overflow up to 33.9 dB compared to operation without AM-MFE. In addition, the ROIC achieves a frame rate of 2.93 kHz, and SNRs of 41.7 and 61.6 dB with 1 and 10 mm metal pillars, respectively.

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This article presents a fully integrated 64-channel programmable ultrasound transmit beamformer for catheter-based ultrasound probes, designed to interface with a capacitive micro-machined ultrasound transducer (CMUT) array. The chip is equipped with programmable high-voltage (HV) pulsers that can generate ±30-V return-to-zero (RZ) and non-RZ pulses. The pulsers employ a compact back-to-back isolating HV switch topology that employs HV floating-gate drivers with only one HV MOS transistor each. Further die-size reduction is achieved by using the RZ switches also as the transmit/receive (T/R) needed to pass received echo signals to low-voltage receive circuitry. On-chip digital logic clocked at 200 MHz allows the pulse timing to be programmed with a resolution of 5 ns, while supporting pulses of 1 cycle up to 63 cycles. The chip has been implemented in 0.18-μm HV Bipolar-CMOS-DMOS (BCD) technology and occupies an area of 1.8 mm ×16.5 mm, suitable for integration into an 8-F catheter. Each pulser with embedded T/R switch and digital logic occupies only 0.167 mm2. The pulser successfully drives an 18-pF transducer capacitance at pulse frequencies up to 9 MHz. The T/R switch has a measured ON-resistance of ~180Ω. The acoustic results obtained in combination with a 7.5-MHz 64-element CMUT array demonstrate the ability to generate steered and focused acoustic beams.

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We proposed a high frame rate 3D imaging scheme for carotid imaging applications. We optimized the transmit and receive sub-aperture sizes to reduce the data rate while providing a sufficient frame rate and image quality for carotid pulse wave and blood flow 3D imaging. In addition, a specific angular weighting function was used in coherent compounding of intermediate images to suppress grating lobes. @en

Miniature ultrasound probes, such as the intra-cardiac echography (ICE) probe shown in Fig. 23.6.1, increasingly employ in-probe ASICs to interface with the elements of an ultrasound transducer array to improve signal quality and reduce cable count [1]-[4]. For each transducer element, such an ASIC contains a pulser that drives the element to generate a pressure wave, a low-noise amplifier (LNA) that amplifies the resulting echo signal, and a time-gain compensation (TGC) circuit that compensates for the time-varying echo-signal amplitude due to propagation attenuation of the acoustic wave. Without TGC, the first echoes, from shallow tissue, are much larger than later echoes from deeper tissue. The TGC circuit corrects for this, ideally by providing a gain that increases exponentially with time, thus reducing the dynamic range (DR) by as much as 40dB and strongly relaxing the requirements of subsequent blocks. In conventional ultrasound systems, TGC is typically performed after the LNA, implying that a power-hungry LNA is required that can handle the full DR of the echo signal [5], [6]. In recent in-probe ASICs, programmable-gain LNAs have been employed that provide a step-wise TGC approximation [1]-[3]. While this saves power, the associated gain-switching transients lead to imaging artefacts. In this paper, we present an LNA with a built-in continuous TGC function that mitigates this problem. The LNA is a transimpedance amplifier (TIA) optimized to amplify the signal current of a capacitive micro-machined ultrasound transducer (CMUT). We demonstrate its integration into a 64-channel ASIC for a CMUT-based ICE probe.

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As the demand for high frame rate and SNR increases in capacitive touch systems (CTSs), several driving methods have been reported [1], [5]. However, when excitation circuits simultaneously send excitation signals V_EXTs to multiple TX electrodes in order to increase frame rate, the readout circuit suffers from charge overflow because of the superposition of V_EXTs. To prevent this, driving methods such as time-division [1], [5] and reduced-amplitude excitation [3], and signal omitting and linear interpolation in the digital domain [4] have been adopted in AFE ICs, but they degrade the frame rate, and SNR, and increase the computational load of the CTS, respectively. In this paper, amplitude-modulated multiple-frequency excitation (AM-MFE) is used to prevent charge overflow without degrading the frame rate, SNR, and computational load. In addition, an electric pencil case (EPC) is proposed for wireless power and data transfer to an active stylus, so as to avoid the need to replace the battery of the stylus or charge it via an adapter.

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This article presents a low-noise transimpedance amplifier (TIA) designed for miniature ultrasound probes. It provides continuously variable gain to compensate for the time-dependent attenuation of the received echo signal. This time-gain compensation (TGC) compresses the echo-signal dynamic range (DR) while avoiding imaging artifacts associated with discrete gain steps. Embedding the TGC function in the TIA reduces the output DR, saving power compared to prior solutions that apply TGC after the low-noise amplifier. The TIA employs a capacitive ladder feedback network and a current-steering circuit to obtain a linear-in-dB gain range of 37 dB. A variable-gain loop amplifier based on current-reuse stages maintains constant bandwidth in a power-efficient manner. The TIA has been integrated in a 64-channel ultrasound transceiver application-specific integrated circuit (ASIC) in a 180-nm BCDMOS process and occupies a die area of 0.12 mm2. It achieves a gain error below ±1 dB and a 1.7 pA/ √ Hz noise floor and consumes 5.2 mW from a ±0.9 V supply. B-mode images of a tissue-mimicking phantom are presented that show the benefits of the TGC scheme.

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We present an ultrasound transceiver ASIC designed for an ultrasound probe for 3-D carotid artery imaging. We propose an improved switch design to minimize the charge-injection effects of high-voltage MOSFETs. @en

In this work, we report the acoustical characterization of a 9 French (Fr) CMUT-based 1D catheter tip (2.5×12.8 mm 2 - 64 elements - 7.5 MHz) embedding a 64 channels analog transceiver ASIC (180 nm HV BCD technology) dedicated to Intra-cardiac Echocardiography. To this end, a Through-Silicon-Via process has been integrated in the CMUT process flow to ensure suitable vertical integration level needed to accommodate with the catheter's form factor. Good overall functioning of essential ASIC functionalities with the CMUT, i.e. transmit, beamforming, and receive, is first reported, starting from elementary characterization up to imaging. Additionally, a comparison with a custom discrete solution based on Commercial Off-The-Shelf components (COTS) to provide suitable CMUT preamplification in receive is performed. Using the same CMUT chip either with the ASIC, either with the COTS, allowed to quantify the benefit brought by the ASIC compared to a more straightforward but less integrated solution. Main results highlight that CMUT-on-ASIC allows to recover a much wider bandwidth (BW), increasing by 3 MHz the -6dB upper limit, and therefore getting closer the theoretical BW of the CMUT itself. Moreover, lower element crosstalk is measured on CMUT-on-ASIC device, showing that the ASIC decreases the electrical coupling compared to the COTS. Finally, noise equivalent pressure measurements in comparison with simulations in realistic ICE configuration promise much higher receive sensitivity with the ASIC solution, hence, confirming its great interest for the CMUT technology compared to less integrated solution, especially for catheter application.@en

To accurately investigate the state of the carotid artery by the local haemodynamics and motion of the plaque using ultrasound, high-frame rate volumetric imaging is necessary. We have specifically designed a matrix array for this purpose. In this proceeding we will focus on imaging a volumetric flow profile using this matrix. For this purpose, we extend a fast frequency domain vector flow imaging method to 3D and perform measurements on a flow phantom. The results indicate that it is feasible to estimate 3D velocity vectors on a 3D grid using our matrix transducer and the proposed algorithm.

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This letter presents a compact programmable high-voltage (HV) pulser for ultrasound imaging, designed for driving capacitive micromachined ultrasonic transducers (CMUTs) in miniature ultrasound probes. To enable bipolar return-to-zero (RZ) pulsing and embedded transmit/receive switching, a compact back-to-back isolating HV switch is proposed that employs HV floating-gate drivers with only one HV MOS transistor each. The pulser can be digitally programmed to generate bipolar pulses with and without RZ, with a peak-to-peak swing up to 60 V, as well as negative and positive unipolar pulses. It can generate bursts of up to 63 pulses, with a maximum pulse frequency of 9 MHz for an 18-pF transducer capacitance. Realized in TSMC 0.18-μm HV BCD technology, the pulser occupies only 0.167 mm ². Electrical characterization results of the pulser, as well as acoustic results obtained in the combination with a 7.5-MHz CMUT transducer, are presented.

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This paper presents an ultrasound transceiver application-specific integrated circuit (ASIC) designed for 3-D ultrasonic imaging of the carotid artery. This application calls for an array of thousands of ultrasonic transducer elements, far exceeding the number of channels of conventional imaging systems. The 3.6 x 6.8 mm² ASIC interfaces a piezo-electric transducer (PZT) array of 24 x 40 elements, directly integrated on top of the ASIC, to an imaging system using only 24 transmit and receive channels. Multiple ASICs can be tiled together to form an even bigger array. The ASIC, implemented in a 0.18 μm high-voltage (HV) BCD process, consists of a reconfigurable switch matrix and row-level receive circuits. Each element is associated with a compact bootstrapped HV transmit switch, an isolation switch for the receive circuits and programmable logic that enables a variety of imaging modes. Electrical and acoustic experiments successfully demonstrate the functionality of the ASIC. In addition, the ASIC has been successfully used in a 3-D imaging experiment.

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Real-time 3D ultrasonic imaging requires a matrix of transducer elements with a number of elements that readily exceeds the number of channels of a conventional imaging system. This paper presents an ASIC, realized in a
high-voltage 0.18 μm BCDMOS process, that interfaces a piezo-electric transducer array of 24 × 40 elements, directly integrated on top of the ASIC, to an imaging system using only 24 transmit and receive channels by means of a reconfigurable switch matrix and row-level low-noise amplifiers. Each element is associated with a compact bootstrapped high-voltage transmit/receive switch and programmable logic that enables a variety of imaging modes to be realized. The ASIC has been successfully used in a 3D imaging experiment.@en

Accurate assessment of carotid artery disease by measuring blood flow, plaque deformation and pulse wave velocity using ultrasound (US) imaging requires 3D information. Additionally, the volume rates should be high enough (> 1 kHz) to capture the full range of these fast transient phenomena. For this purpose, we have built a programmable, tileable matrix array that is capable of providing 3D US imaging at such volume rates. This array contains an application-specific integrated circuit (ASIC) right beneath the acoustic piezo-stack (see Fig. 1a). The ASIC enables fast programmable switching between various configurations of elements connected to the acquisition system. This design also allows for expanding the footprint by tiling several of these arrays together into one large array. We explain the working principles and show the first basic imaging results of a single matrix array.

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Accurate assessment of carotid artery disease by measuring blood flow, plaque deformation and pulse wave velocity using ultrasound imaging requires 3D information. Additionally, the volume rates should be high enough (> 1 kHz) to capture the full range of these fast transient phenomena. For this purpose, we have built a programmable, tileable matrix array that is capable of providing 3D ultrasound imaging at such volume rates. This array contains an application-specific integrated circuit (ASIC) right beneath the acoustic piezo-stack. The ASIC enables fast programmable switching between various configurations of elements connected to the acquisition system via a number of channels far smaller than the number of transducer elements. This design also allows for expanding the footprint by tiling several of these arrays together into one large array. We explain the working principles and show the first basic imaging results of a 2-by-1 tiled array.

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