Wireless biosensors are playing a pivotal role in health monitoring, disease detection and management. The development of wireless biosensor nodes and networks strongly relies on the design of novel low-power, low-cost and flexible CMOS sensor readouts. This brief presents a CMOS potentiostat that integrates a control amplifier, a dual-slope ADC and a wireless unit on the same chip. It implements a novel time-based readout scheme, whereby the counter of the dual-slope ADC is moved to the receiver and the sensor current is encoded in the timing between two wireless pulses transmitted via pulse-harmonic modulation across an inductive link. Measured results show that the potentiostat chip can resolve a minimum input current of 10pA at a sampling frequency of 125 Hz and a power consumption of 12 μW .

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Wireless data telemetry for implantable medical devices (IMDs) has, in general, been limited to a few Mbps, and used for applications such as transmitting recordings from an implanted monitoring device, or uploading commands to an implanted stimulator. However, modern neural interfaces need to record high resolution potentials from hundreds of neurons; this requires much higher data rates. While fast wireless communication is possible using existing standards such as WiFi, power consumption demands are far too high for IMDs. Short range inductive link based telemetry, in particular impulse-based systems such as pulse-harmonic modulation (PHM), have demonstrated transfer speeds of up to 20 Mbps with a small power budget. However, these systems require complex and precise circuits, making them potentially susceptible to inter-symbol-interference. This work presents a new method named Short-range Quality-factor Modulation (SQuirM), which retains the low power consumption and high data rate of PHM, while improving the resilience of the system and simplifying the circuit design. Transmitter and receiver circuits were fabricated using 0.35 μm CMOS. The circuits were capable of reliably transceiving data at speeds of up to 50.4 Mbps, with a BER of < 4.5 × 10^-10 , and a transmitter energy consumption of 8.11 pJ/b.

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The original paper entitled "Practical Inductive Link Design for Biomedical Wireless Power Transfer: A Tutorial" [1], aimed to provide an accessible review and guide, describing the necessary steps for designing effective biomedical inductive links, without the need for FEM Software. While the majority of the information in this paper is accurate and applicable, some errors in formulas have been brought to the attention of the authors, which could generate erroneous results if used in calculations. The aim of this paper is to highlight and correct these errors. It should be noted that the accompanying software for performing these calculations has also been corrected where necessary, in line with the corrections presented here [2]. The errors largely relate to the equations presented throughout, and are listed below: First, [1, Eq. (2)], defining an approximation for Nagaoka's coefficient, contains erroneous squares and is missing a term in the fraction of the large denominator. The correct form is presented below: Second, [1, Eq. (14)] considers the ac losses of a Litz-wire coil. The original form contains errors of coefficients and signs. The correct formulation is given as follows: (Formula presented). Third, [1, Eq. (17)] is missing a square. The correct form is as follows: Fourth, [1, Eq. (26)], that defines ang, is missing a cos a from the numerator of the top fraction under the square root. The correct form is given below: Finally, the caption of [1, Fig. 17] is in error; it currently refers to coupling coefficient, while it shows Q-factor. It should read as follows: "Changing Q-factor as winding pitch is modified, with respect to frequency.

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Short-range, low-power, high data-rate telemetry is an increasingly desirable feature for implantable medical devices (IMDs), and is commonly implemented using an inductive link. Pulse Harmonic Modulation (PHM) provides the desired high data rates and low power consumption, but requires precise pulse timing. This paper presents a modification of PHM, Single-Pulse Harmonic Modulation (SPHM), which offers reduced power consumption and lower implementation complexity. In order to test the SPHM concept, transmitter and receiver circuits were designed in 0.35μm CMOS and simulated. The simulated results suggest that the circuits can transceive data at 50Mb/s, consuming 1.49pJ/b and 2.59pJ/b at the transmitter and receiver respectively, from a 1.2V supply.

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Wireless sensing systems are becoming popular in a range of applications, particularly in the case of biomedical circuits and food monitoring systems. A typical wireless sensing system, however, may require considerable complexity to perform the necessary analog to digital conversion and subsequent wireless transmission. Alternatively, in the case of inductive link based systems, large, manually operated impedance analyzers are required. Based on a detailed analysis of the link impedance, this paper proposes a simple method for wireless capacitive sensing through an inductive link that uses a self-oscillator and a frequency counter. The method enables changes in capacitance to be sensed and wirelessly transmitted simultaneously. In order to test the effectiveness of the method, a self-oscillating circuit was designed and fabricated in 0.18 &#x03BC;m CMOS, and combined with an on-chip humidity sensing capacitor. The system was tested in a humidity chamber across a range of 20-90&#x0025;rh. Measured results from the system demonstrate that capacitive changes as small as 28 fF, translating to &lt;2&#x0025;rh, can be resolved, with a power consumption of 1.44 mW.

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Point-of-care (PoC) diagnostics rely on the design of low-power and miniaturized readout units that can offer rapid and accurate test results, replacing the need for specialized equipment. CMOS technology can be exploited in order to design complex systems while achieving high energy efficiency for suitable operation in a mobile settings. This paper presents the design of a novel energy-efficient 4-channel wireless potentiostat chip, based on a dual-slope ADC architecture, that features a low-complexity wireless unit and a calibration approach that does not require additional circuitry. The chip was designed in a 0.35μm CMOS process. The simulated results suggest that each potentiostat channel can achieve an estimated energy efficiency of 2.5 pJ/bit from a 1.2 V supply.@en

There is growing demand for circuits that can provide ever greater performance from a minimal power budget. Example applications include wireless sensor nodes, mobile devices, and biomedical implants. High speed clock circuits are an integral part of such systems, playing roles such as providing digital processor clocks, or generating wireless carrier signals; this clock generation can often take a large part of a system's power budget. Common techniques to reduce power consumption generally involve reducing the clock speed, and/or complex designs using a large circuit area. This paper proposes an alternative method of clock generation based on driving a high-Q resonator with a periodic chain of impulses. In this way, power consumption is reduced when compared to traditional resonator based designs; this power reduction comes at the cost of increased period jitter. A circuit was designed and laid out in 0.18μm CMOS, and was simulated in order to test the technique. Simulation results suggest that the circuit can achieve a FoM of 4.89GHz/mW, with a peak period jitter of 10.2ps at 2.015GHz, using a model resonator with a Q-factor of 126.@en

Wireless power transfer systems, particularly those based on inductive coupling, provide an increasingly attractive method to safely deliver power to biomedical implants. Although there exists a large body of literature describing the design of inductive links, it generally focuses on single aspects of the design process. There is a variety of approaches, some analytic, some numerical, each with benefits and drawbacks. As a result, undertaking a link design can be a difficult task, particularly for a newcomer to the subject. This tutorial paper reviews and collects the methods and equations that are required to design an inductive link for biomedical wireless power transfer, with a focus on practicality. It introduces and explains the published methods and principles relevant to all aspects of inductive link design, such that no specific prior knowledge of inductive link design is required. These methods are also combined into a software package (the Coupled Coil Configurator), to further simplify the design process. This software is demonstrated with a design example, to serve as a practical illustration.

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Point-of-care systems for the detection of infectious diseases are in great demand especially in developing countries. Lateral flow immunoassays are considered ideal biosensors for point-of-care diagnostics due to their numerous advantages. However, to quantify their results a low power, robust electronic reader is needed. A low power CMOS image sensor is presented that can be used in quantitative lateral flow immunoassay readers. It uses a single low power processing capacitive transimpedance amplifier architecture which includes noise cancellation. A chip containing 4 &#x00D7; 64 pixels was fabricated in CMOS 0.35-&#x03BC;m technology. With uniform illumination at 525 nm and 67 frames per second the chip has 1.9 mVrms total output referred noise and a total power consumption of 21 &#x03BC;W. In tests with lateral flow immunoassays the chip detected concentrations of influenza A nucleoprotein from 0.5 ng/mL to 200 ng/mL.

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A novel pixel architecture for CMOS image sensors is presented. It uses only one amplifier for both integration of the photocurrent and in-pixel noise cancelation, thus minimizing power consumption. The circuit is specifically designed to be used in readout systems for lateral flow immunoassays. In addition a switching technique is introduced enabling the use of column correlated double sampling technique in capacitive transimpedance amplifier pixel architectures without the use of any memory cells. As a result the reset noise which is crucial in these architectures can be suppressed. The circuit has been designed in a 0.35-μm CMOS technology and simulations are presented to show its performance.@en

This paper presents the design of a 1024-channel dual-modality CMOS biosensor suitable for both capacitive sensing and impedance spectroscopy. The chip serves as a platform for detection, localization and monitoring of bacteria and can be adopted for affinity-based assays. The chip features a 32×32 array of unpassivated metal electrodes formed on the top metal of a 0.18μm CMOS process, with an overall sensing area of 2.06 mm2. The system design is based on a shared in-pixel integrator that can be used as a charge amplifier for capacitive sensing (CS) or as part of a transimpedance amplifier for electrical impedance spectroscopy (EIS). The CS mode is capable of a operation bandwidth of 50 MHz at a current consumption of 82 μA per pixel. The EIS channel operates over a bandwidth between 100 Hz and 1 MHz with a total input-referred current noise of 48 pArms and a current consumption of 210 μA per channel.

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This paper presents a multi-channel dual-mode CMOS analogue front-end (AFE) for electrochemical and bioimpedance analysis. Current-mode and voltage-mode readouts, integrated on the same chip, can provide an adaptable platform to correlate single-cell biosensor studies with large-scale tissue or organ analysis for real-time cancer detection, imaging and characterization. The chip, implemented in a 180-nm CMOS technology, combines two current-readout (CR) channels and four voltage-readout (VR) channels suitable for both bipolar and tetrapolar electrical impedance spectroscopy (EIS) analysis. Each VR channel occupies an area of 0.48 mm², is capable of an operational bandwidth of 8 MHz and a linear gain in the range between -6 dB and 42 dB. The gain of the CR channel can be set to 10 kΩ, 50 kΩ or 100 kΩ and is capable of 80-dB dynamic range, with a very linear response for input currents between 10 nA and 100 μA. Each CR channel occupies an area of 0.21 mm². The chip consumes between 530 μA and 690 μA per channel and operates from a 1.8-V supply. The chip was used to measure the impedance of capacitive interdigitated electrodes in saline solution. Measurements show close matching with results obtained using a commercial impedance analyser. The chip will be part of a fully flexible and configurable fully-integrated dual-mode EIS system for impedance sensors and bioimpedance analysis.

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This paper presents a fully implantable multi-channel neural prosthesis for epidural stimulation. The prosthesis features three telemetry-operated independent stimulators providing in total eighteen stimulation channels. The stimulator circuits were implemented in a 0.6-μm CMOS technology. The prosthesis is protected in a hermetically sealed ceramic enclosure and encapsulated in medical grade silicone rubber. In-vitro measured results with electrodes in saline are presented.

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A fully implantable multi-channel neural prosthesis for epidural stimulation will be demonstrated. The prosthesis features three telemetry-operated independent stimulators providing in total eighteen stimulation channels. The stimulator circuits were implemented in a 0.6-μm CMOS technology. The prosthesis is protected in a hermetically sealed ceramic enclosure and encapsulated in medical grade silicone rubber for long-term implantation. During the live demonstration in-vitro tests with electrodes in saline will be performed with the prosthesis operated wirelessly from a remote computer.

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Clinical deep brain stimulation (DBS) uses 4 cylindrical electrodes driven in monopolar or bipolar configurations. This yields a spherical stimulation field around the electrode modulating both targeted and untargeted areas. This paper presents an approach in which activation field spread beyond targeted areas can be mitigated using dynamic current steering. Dynamic current steering uses segmented electrodes together with dynamic current sources in order to accurately stimulate intended neural tissue. This paper will focus on the output stage of the dynamic current steering system. The output stage uses dynamic current sources (DCS) in implementing 8 push-pull current sources that are interfaced to 16 electrodes so as to enable current steering. The dynamic current sources operate in two phases - programming and stimulation. This technique was adopted because it reduces power consumption and output current mismatch. The 16 electrodes can be driven both as anodes and cathodes. As a proof of concept the stimulator uses a supply of 3.3 V to drive biphasic current pulses of up to 0.5 mA through its electrodes. The circuit was implemented in a 0.18 μm CMOS technology.

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This paper presents the operation of a dualmode wideband CMOS analog front-end (AFE) for electrical impedance spectroscopy. The chip combines two current-readout (CR) channels and four voltage-readout (VR) channels suitable for both bipolar and tetrapolar EIS analysis. The chip addresses the need for flexible readout units for real-time simultaneous single-cell and large scale tissue/organ analysis. Postlayout simulations show that the VR channel is capable of wideband operation up to 12 MHz with noise floor as low as 16.4 nV/Hz^1/2. A 2-bit control allows to select between a high-frequency low-gain channel and a bandwidth-limited high-gain channel. Each VR channel occupies an area of 0.48 mm². The CR channel is capable of 80 dB of dynamic range, by converting currents between 1 nA to 10μA, while achieving a noise floor of 1.4 pA/Hz^1/2. An automatic gain control (AGC) unit can be enabled in order maintain the sensor signal within the ADC dynamic range. Each CR channel occupies an area of 0.21 mm². The chip consumes between 290 μA and 690 μA per channel and operates from a 1.8 V supply. The chip will be part of a fully flexible and configurable dual-mode EIS systems for impedance sensors and bioimpedance analysis.

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This paper presents a second-generation integrated circuit for the Active Books neural stimulation microsystem. It provides multi-channel stimulation with versatile control of stimulation profiles and reduced crosstalk from other stimulation channels. The new design features enhanced safety by monitoring the temperature and humidity inside the micropackage, and the peak electrode voltage at any stimulating electrode. The humidity sensor uses an interdigitated capacitor covered by a passivation layer and a polyimide covering. To boost sensitivity in the operating range of interest, the temperature sensor uses a temperature-insensitive current that is subtracted from a proportional-to-absolute-temperature current. A 3-b analog-to-digital converter is used to record the peak electrode voltage. All sensor data is sent to an implanted central hub using bidirectional connection with error checking. Both the stimulation electronics and sensors are integrated on a 6.2 mm 4 mm silicon die using XFAB's 0.6- μ m CMOS high-voltage process. No post-processing steps are involved. The stimulator uses a five-wire cable to provide the power supply and bidirectional data signals. The chip operates from a 7.5-18 V power supply and can generate stimulation currents of 1 mA, 4 mA or 8 mA with a pulse duration of 2 μ S-1.07 ms. The humidity sensor output varies linearly with relative humidity (RH) with a normalized sensitivity of 0.04%/%RH over the range of 20-90%RH. The temperature sensor has a nonlinearity of 0.4% over the range of 20-90 °C and a resolution of 0.12 °C. The stimulator is the first of its kind to include integrated temperature and humidity sensors.@en

Inductive powering for implanted medical devices, such as implantable biosensors, is a safe and effective technique that allows power to be delivered to implants wirelessly, avoiding the use of transcutaneous wires or implanted batteries. Wireless powering is very sensitive to a number of link parameters, including coil distance, alignment, shape, and load conditions. The optimum drive frequency of an inductive link varies depending on the coil spacing and load. This paper presents an optimum frequency tracking (OFT) method, in which an inductive power link is driven at a frequency that is maintained at an optimum value to ensure that the link is working at resonance, and the output voltage is maximised. The method is shown to provide significant improvements in maintained secondary voltage and system efficiency for a range of loads when the link is overcoupled. The OFT method does not require the use of variable capacitors or inductors. When tested at frequencies around a nominal frequency of 5 MHz, the OFT method provides up to a twofold efficiency improvement compared to a fixed frequency drive. The system can be readily interfaced with passive implants or implantable biosensors, and lends itself to interfacing with designs such as distributed implanted sensor networks, where each implant is operating at a different frequency.

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Inductive powering for implanted medical devices is a commonly employed technique, that allows for implants to avoid more dangerous methods such as the use of transcutaneous wires or implanted batteries. However, wireless powering in this way also comes with a number of difficulties and conflicting requirements, which are often met by using designs based on compromise. In particular, one aspect common to most inductive power links is that they are driven with a fixed frequency, which may not be optimal depending on factors such as coupling and load. In this paper, a method is proposed in which an inductive power link is driven by a frequency that is maintained at an optimum value f_opt , to ensure that the link is in resonance. In order to maintain this resonance, a phase tracking technique is employed at the primary side of the link; this allows for compensation of changes in coil separation and load. The technique is shown to provide significant improvements in maintained secondary voltage and efficiency for a range of loads when the link is overcoupled.

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