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California amplifier planar transceiver kit

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Journal of Translational Medicine volume 15 , Article number: Cite this article. Metrics details. Magnetic resonance is a major preclinical and clinical imaging modality ideally suited for longitudinal studies, e. The lack of a proven platform that maintains an identical imaging protocol between preclinical and clinical platforms is solved with the construction of an animal scanner based on clinical hard- and software.

A small animal magnet and gradient system were connected to a clinical MR system. Several hardware components were either modified or built in-house to achieve compatibility. The clinical software was modified to account for the different field-of-view of a preclinical MR system. The established scanner was evaluated using clinical QA protocols, and platform compatibility for translational research was verified against clinical scanners of different field strength.

The constructed animal scanner operates with the majority of clinical imaging sequences. Translational research is greatly facilitated as protocols can be shared between preclinical and clinical platforms. Hence, when maintaining sequences parameters, maximum similarity between pulses played out on a human or an animal system is maintained. Coupling of a small animal magnet with a clinical MR system is a flexible, easy to use way to establish and advance translational imaging capability.

It provides cost and labor efficient translational capability as no tedious sequence reprogramming between moieties is required and cross-platform compatibility of sequences facilitates multi-center studies.

It is the preferred method to monitor disease progression and response to treatment in small-animal models in basic and preclinical science and acts as a bridge between novel discoveries and clinical implementation in patient treatment.

While small rodent imaging can be carried out on human MRI scanners, dedicated small animal systems display performance benefits such as higher temporal and spatial resolution [ 8 ]. However, these dedicated systems usually operate with vendor specific software and require the reimplementation of MR sequences to facilitate translational imaging studies. In addition to the tedious reprogramming of the MRI sequences in another programming environment, this approach is also prone to creating mismatching sequences and consequently creating experimental discrepancies, which reduce translational validity.

That this is in fact problematic is obvious from early reports on—e. While there are currently only a few dedicated vendors for preclinical MRI systems, new companies are emerging, hoping to capitalize on the potential market. However, due to cost and complexity, advanced animal imaging sequences may not be readily available on all systems and will differ in their implementation. Shrinking the gap between preclinical and clinical studies, while changing experimental parameters as little as possible, makes transposition of data easier.

Thus the development of a dedicated small animal MRI machine using clinical software presents a major step in bridging this gap for truly translational research. According to Tsui et al. Most prominent areas are drug discovery, e. Here, the construction and operation of a unique 9. It operates with clinical software and allows execution of sequences compiled for the analogous human MRI scanner family. An initial report of this work has been presented at the 24th International Conference of the Society of Magnetic Resonance in Medicine [ 14 ].

Figure 1 shows a system overview containing the major MR hardware components. However, several modifications were required and these are described in more detail below. The solution presented is based on modifying software parameters only and can potentially be upgraded to forthcoming new software baselines. Furthermore, it is capable of performing non-proton MR measurements, such as 23 Na and 31 P and is currently being extended to facilitated parallel transmission.

System overview showing major components and interconnections. In contrast to human high field systems this machine is equipped with a body coil. Specifically designed components have a green background, modified parts are marked with a color transition while untouched components have a while background.

As in-house research takes place on a 9. A suitable 9. It has a free bore of mm and was initially configured with a double cryostat filled with liquid helium and liquid nitrogen, respectively. However, it was retrospectively fitted with a pulse tube cryocooler Cryomech, Inc. Syracuse, USA that achieves zero boil-off operation and consequently only required that the nitrogen cryostat be filled with helium gas. The original magnet supervision and emergency discharge unit supplied by the magnet vendor was maintained without integrating these into the clinical system.

Although integration is technically feasible, the interface between the different supervision units is complex and would not significantly alleviate system handling. In addition to the inherent demand for high gradient strength and slew rate, the requirements for the gradient insert are mechanical compatibility with the magnet dimensions; an inner diameter suitable for measuring small animals, e.

Compatibility with the clinical gradient amplifiers was found to be essential, as the gradient amplifiers of a standard clinical system are designed for the strong drive requirements of large volume human gradient coils.

However, by disabling single stages of the multiple-stage H-bridge amplifier configuration, it was possible to reduce the maximum output power of the gradient amplifiers. Following these modifications, the current output capability of each gradient amplifier was reduced to a maximum of approx. Palo Alto, USA. The later was chosen for the system described here. Further hardware modifications of the gradient amplifier system were made on the ohmic loss supervision and the maximum pulse length supervision, depending on the applied output current.

This was accomplished by modifying the analogue supervision circuitry of the gradient amplifiers and required changing resistor values in the operational amplifier based integration circuits. In addition, the temperature of the gradient insert is monitored using integrated PT temperature sensors and a vendor supplied monitoring circuit connected to a novel interface unit that sends a temperature interlock signal to the clinical MR system Fig.

As an additional safeguard, gas discharge units were connected in parallel to the gradient coils in order to protect them in case the gradient amplifiers exceeded the maximum voltage settings e. A vendor supplied CAN-bus Controller Area Network—a standardised serial bus system to reduce wire count to serial interface was used to connect the shim amplifiers to the MR scanner. The RF power amplifiers barthel HF-Technik GmbH, Aachen, Germany were specifically designed for the platform described here and consist of a narrowband amplifier for protons and a broadband amplifier for X-nuclei, each capable of delivering 1 kW peak power.

The proton amplifier combines the output power of four independent W units—a design option chosen to facilitate later extension of the system for parallel transmit operation. The X-nucleus amplifier covers a frequency range from 50 to MHz, which allows imaging of the most biologically relevant nuclei, such as 13 C, 17 O, 23 Na and 31 P.

It is important to note that the proton amplifier also covers the 19 F frequency of approx. Both power amplifiers were integrated into the clinical MR platform through a CAN bus interface, which was developed by the manufacturer of the amplifiers. In contrast to human high field scanners, the animal system is equipped with a body-coil.

This conventional system setup is appropriate since wavelength effects in small animal systems are less pronounced due to the smaller size of imaged objects. The body-coil is a self-shielded, 8-rung, high-pass quadrature birdcage with a free inner diameter of 74 mm Fig. Capacitors are 4. It can also be detuned statically in case local transmitter coils are used for excitation.

Local coils, e. Each connector supports up to eight receive channels with the front connector being equipped with a proton transmit and the back connector with an additional X transmit channel. The available X-nucleus imaging coil set has been described previously [ 15 ]. All coils are detected by their unique coil code and the system automatically sets PIN diode control and sequence parameters according to the connected coil systems, as known from clinical routine.

Animal handling includes the table shown in Fig. The animal bed includes a facemask for gas anesthesia, which is connected to a standard veterinarian vaporizer A. Bickford, Inc. Animal supervision, allowing the acquisition of ECG, respiration and temperature, uses a commercially available monitoring system Small Animal Instruments, Inc.

The system provides a user configurable trigger signal that is interfaced to the MRI scanner to enable synchronized sequences using the ECG or breathing signals of the animal. Due to both its use as a translational platform and the complexities involved in reprogramming, an important requirement of the animal MR scanner is that it can be operated with only minor tweaks to the measurement parameters and without having to modify major parts of its software.

Ordinarily two major modifications would be required relating to field-of-view FoV settings of an animal system compared to a human scanner and hardware component differences.

The latter was addressed by disabling software supervision of non-existing components, e. FoV settings were amended by introducing a scaling of linear dimensions. By doing this, the FoV discrepancy was reduced to an extent that the clinical software worked with the smaller imaging dimensions of the animal system.

The scaling was implemented by modifying gradient and shim sensitivities accordingly. In addition, the system tune-up also required several parameter modifications. The most prominent being, definition of tune-up phantoms used with the animal system, modification of hardware supervision such as minimum flow of cooling water through the gradient insert, and a reduction of the transmit power limits to account for the less potential power amplifies in an animal environment.

Modification of parameters is carried out by changing these in the measurement settings file of the clinical MR software. Several experiments were carried out after establishing system validity based on clinical quality assurance QA routines to validate the translational workflow. In all cases, compiled sequences were copied on both systems and data acquired using a clinical scanner as well as the animal platform is presented here.

For comparative purposes, the basic MR sequences—spin-echo and gradient-echo—were employed as they are the building blocks for all advanced imaging sequences.

A set of phantom images was acquired using a standard spin echo sequence with isotropic resolution. Details of the imaging parameters are shown in Table 1.

The phantoms employed were a mm diameter spherical plastic phantom filled with doped water 1. All images were acquired with the body-coil of the respective MRI system. As a second test-case, images were also acquired with the vendor supplied gradient echo sequence at 9. Sequence parameters for the acquisition at the same field strength were kept identical, except for resolution and slice thickness, which were adapted to the desired FoV compare Table 1.

Due to the wavelength effect associated with the larger dimensions of the human body the 9. Advanced imaging experiments were carried out on the animal scanner only to validate its performance using state of the art MR sequences.

The first investigation images a rat spinal cord using a turbo-spin-echo sequence with gating on the animal breathing. The sequence employed is derived from a clinical T 1 weighted spinal cord sequence.

Modifications required for 9. The second analysis uses an echo planar readout for a single shot acquisition of the 40 mm diameter phantom described above to demonstrate gradient performance in the scope of combining clinical and non-clinical hardware. The EPI sequence was derived from a clinical sequence supplied by the vendor and sequence parameters optimized for the small animal system compare Table 1. Finally, quantitative performance measures were acquired to evaluate static and RF field homogeneity of the system.

Based on the principles described in [ 18 ] B 0 field maps were generated. The field map data was acquired using a standard multi-echo GRE sequence.


Recent Progress in Heterogeneous III-V-on-Silicon Photonic Integration

Figures Heterogeneous photonics integration: recent breakthroughs and progressive perspective. Integrated photonics was rejuvenated as silicon starting challenging the dominant status of conventional III-V compound semiconductors at onset of the new millennium. Heterogeneous III-V-on-silicon integration provides an ideal platform to marry their respective material and production advantages. Two veteran researchers in this field, Di Liang from Hewlett Packard Labs and John Bowers from University of California - Santa Barbara, carefully reviewed a number of recent breakthroughs to show how this novel concept has evolved from a science project 15 years ago to a growing business and compelling research field today. It includes both commercial successes in optical transceivers and new research directions in materials, device designs and integration platform innovations.

For example, I was scanning the ads for a high-power ham-radio amplifier. Most of the popular transceivers top out at about W. For good.

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california amplifier planar transceiver kit

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Low to medium power valve amplifiers for frequencies below the microwaves were largely replaced by solid state amplifiers during the s and s, initially for receivers and low power stages of transmitters, transmitter output stages switching to transistors somewhat later. Specially constructed valves are still in use for very high power transmitters, although rarely in new designs.

Improved adaptive impedance matching for RF front-end systems of wireless transceivers


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9.4 T small animal MRI using clinical components for direct translational studies

He completed his B. His research interests are focused on semiconductor devices and microsystems for sensing applications. He has published over papers on sensor and photonic technologies, mainly with an emphasis on integration of technologies. The Microsystem Technology group is funded by several major grants and delivers research in medical sensors and systems, CMOS integrated circuits and biosensors, VLSI design for sensor applications, lab-in-a-pill, imaging technology for visible, mid-IR and terahertz applications, nanotechnology and photonics, including metamaterials and surface plasmon resonance. DC is active in several fields including terahertz technology, nanofabrication and VLSI design for sensors. Xie, C. Patil, S. Biosensors and Bioelectronics , , pp.

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Journal of Translational Medicine volume 15 , Article number: Cite this article. Metrics details. Magnetic resonance is a major preclinical and clinical imaging modality ideally suited for longitudinal studies, e. The lack of a proven platform that maintains an identical imaging protocol between preclinical and clinical platforms is solved with the construction of an animal scanner based on clinical hard- and software.

Parts obsolescence is a real issue in high-reliability electronics like aerospace and defense systems.

By integrating it all into silicon, we are taking advantage of the scale, costs, and process control of silicon manufacturing. By Dave Lammers. The ramp-up comes in time to make a single-chip SiPh design from a key partner, California-based startup Ayar Labs, which has created a monolithic design that sets new benchmarks for package-to-package interconnect in terms of bandwidth, power consumption, and latency. For several years GF has been building components for optical transceivers with its silicon-germanium process 9HP at its Fab 9 near Burlington, Vermont. Optical connections are set to move to a new phase, in which the pluggable optical transceivers are replaced by having the photonics link connected to a high-performance IC in the same package, with an external laser providing the light source. That package connects over fiber to another module with a photonics link, creating package-to-package interconnects at high speeds and much lower power consumption.

Vertically polarized, with 2. Vertically polarized, omnidirectional planar antenna with 2 dBi gain 2. There are certain patch ranges within kernels 4.




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