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Ektelon Vendetta Racquetball Eyewear
Product Information:
Get a durable, stylish frame for your next racquetball or squash match with the Ektelon Vendetta Racquet Eyewear. The Vendetta glasses feature a lightweight design to make it easy to put on and take off. Anti-fog treated lenses prevent fogging even during the steamiest matches, while the adjustable head strap provides a customized fit. Micro fiber cleaning pouch included.
- Lightweight composite eyewear
- Hinged, adjustable side arms to give you the fit you need
- Anti-fog treated lenses
- Adjustable head strap for a customized fit
- Micro fiber cleaning pouch included
- Model: 6E826020ST
- Ektelon
Country of Origin: ChinaWeb ID: 3982094
Customer Reviews:
Rated 4.3 out of 5�by 4 reviewers.
Rated 4 out of 5�by wsv works well This eyewear works well and has good features. I would purchase again. June 12, 2013
Rated 5 out of 5�by Shelly Perfect for a soccer goalie! These work great for my daughter, when she plays goalie! April 24, 2013
Rated 3 out of 5�by caroflute Uncomfortable! No problem with fogging, are distortion free, and were fine for the first couple wearings. After that they became loose and kept sliding down my face. They also pinch my head, giving me a headache. I can't wear them any longer. January 29, 2013
Rated 5 out of 5�by bribri36 Great for Ball Hockey I have been using these for ball hockey for several weeks and have had no problems. They stay very clear and the vent holes help to avoid steam build up. They even survived a head butt! Great product for the price! December 5, 2012
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subset: commoncrawl


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|Publication number
|Publication type
|Application number
|Publication date
|Mar 22, 2005
|Filing date
|Oct 21, 2002
|Priority date
|Oct 19, 2001
|Fee status
|Also published as
|Publication number
|Varouj Amirkhanian, Ming-Sun Liu
|Original Assignee
|Biocal Technology, Inc.
|Export Citation
|BiBTeX, EndNote, RefMan
|Patent Citations (55), Non-Patent Citations (16), Referenced by (70), Classifications (7), Legal Events (5)
|External Links: USPTO, USPTO Assignment, Espacenet
This application is a continuation-in-part and claims the priority of the following: (a) U.S. Provisional Patent Application No. 60/348,034, filed Oct. 19, 2001; (b) U.S. patent application Ser. No. 10/060,052, filed Jan. 28, 2002; and (c) U.S. patent application Ser. No. 10/059,993, filed Jan. 28, 2002. These applications are fully incorporated by reference as if fully set forth herein.
1. Field of the Invention
The present invention relates to detection techniques in bio-analysis, particularly optical detection in a multi-channel bio-separation system, and more particularly detection of emissions from radiation excitations in multi-channel capillary based electrophoresis. The present invention further relates to bio-separation instrument incorporating the detection scheme of the present invention.
2. Description of Related Art
Bioanalysis, such as DNA analysis, is rapidly making the transition from a purely scientific quest for accuracy to a routine procedure with increased, proven dependability. Medical researchers, pharmacologists, and forensic investigators all use DNA analysis in the pursuit of their tasks. Yet due to the complexity of the equipment that detects and measures DNA samples and the difficulty in preparing the samples, the existing DNA analysis procedures are often time-consuming and expensive. It is therefore desirable to reduce the size, number of parts, and cost of equipment, to make easy sample handling during the process, and in general, to have a simplified, low cost, high sensitivity detector.
One type of DNA analysis instruments separates DNA molecules by relying on electrophoresis. Electrophoresis techniques could be used to separate fragments of DNA for genotyping applications, including human identity testing, expression analysis, pathogen detection, mutation detection, and pharmacogenetics studies. The term electrophoresis refers to the movement of a charged molecule under the influence of an electric field. Electrophoresis can be used to separate molecules that have equivalent charge-to-mass ratios but different masses. DNA fragments are one example of such molecules.
There are a variety of commercially available instruments applying electrophoresis to analyze DNA samples. One such type is a multi-lane slab gel electrophoresis instrument, which as the name suggests, uses a slab of gel on which DNA samples are placed. Electric charges are applied across the gel slab, which cause the DNA sample to be separated into DNA fragments of different masses.
Another type of electrophoresis instruments is the capillary electrophoresis (CE) instrument. CE refers to a family of related analytical techniques that uses very strong electric fields to separate molecules within narrow-bore capillaries (typically 20-100 um internal diameter). CE techniques are employed in seemingly limitless applications in both industry and academia. Gel- and polymer network-based CE has revolutionized studies of nucleic acids; applications include DNA sequencing, nucleotide quantification, and mutation/polymorphism analysis. By applying electrophoresis in a fused silica capillary column carrying a buffer solution, the sample size requirement is significantly smaller and the speed of separation and resolution can be increased multiple times compared to the slab gel-electrophoresis method. These DNA fragments in CE are often detected by directing light through the capillary wall, at the components separating from the sample that has been tagged with a fluorescence material, and detecting the fluorescence emissions induced by the incident light. The intensities of the emission are representative of the concentration, amount and/or size of the components of the sample.
Some of the challenges in designing CE-based instruments and CE analysis protocols relates to sample detection techniques. In the case of fluorescence detection, considerable design considerations had been given to, for example, radiation source, optical detection, sensitivity and reliability of the detection, cost and reliability of the structure of the detection optics.
CE with the use of the fluorescence method provides high detection sensitivity for DNA analysis. Fluorescence detection is often the detection method of choice in the fields of genomics and proteomics because of its outstanding sensitivity compared to other detection methods. Two prevailing fluorescence detection modes are confocal scanning laser induced fluorescence (LIF) and sheath flow detectors.
The main drawback of the sheath flow detector is the highly sophisticated flow system needed to ensure a reliable sheath flow. Extreme demands are put on the optical and mechanical component tolerances in order to meet the robustness demands of end-users. The sensitivity of the device is very good, but it is not obvious that this principle of fluorescence detection is suited for a high-throughput yet low cost DNA analysis. The scanning confocal detector is based on scanning the optical system. The use of moving parts is not ideal when considering simplicity, robustness and lower cost of the instrument. Also, the shallow focal depth of the microscope objective puts severe demands on the mechanical and optical component tolerances. Further, the optical scanning principle reduces the duty cycle per capillary, which may impair the sensitivity when scaling up the instrument further for very high-throughput purposes.
One of the most expensive hardware components for many commercially available CE instruments with LIF detector is typically a fluorescence excitation light source, which can be a gas discharge lamp (mercury or xenon) or a laser (gas, solid state with second harmonic generation, dye, or semiconductor), that are bulky, expensive, inefficient and difficult to couple one's light output into optical fibers, thus preventing miniaturization of the optical detection system. These light sources hinder development of small size, high-throughput and cost-effective analytical instruments, with the convenience required for rapid detection.
Separation of DNA fragments by size using gel-filled capillaries has advantages over the classical slab gel-based separations in terms of speed and resolution. However, most commercially available CE instrumentation has only one capillary, and only one sample may be analyzed at a time. In a commercial automated DNA sequencer utilizing a slab gel system (such as the Applied BioSystems 377 instrument), 36 samples may be analyzed simultaneously. In order for capillary electrophoreis based DNA fragment analyzing instrumentation to be competitive on a throughput basis, it has been necessary to develop instruments that can run more than one sample at a time. The principle involved in DNA fragment Analyzing instruments (such as PACE 5000 LIF, PACE MDQ LIF of Beckman Coulter) using a single-capillary instrument can be extended to multi-capillary system. However, the design of a multi-capillary DNA Analyzer utilizing LIF based detection optical systems (i.e. 8-capillary CEQTM 2000XL Instrument of Beckman Coulter) are considerably more costly and complicated than the classical slab gel-based systems. Other examples of commercially available multi-capillary CE instruments include instruments developed by ABI, SpectruMedix and Pharmecia, which shared similar drawbacks.
Another fluorescence detection method illuminates the interiors of multiple capillaries simultaneously, and collects the light emitted from them. As in U.S. Pat. No. 5,790,727, the capillaries in a parallel array form an optical wave guide wherein refraction at the cylindrical surfaces confines illuminating light directed in the plane of the array to the core of each adjacent capillary in the array. However, because only one light source is used for the illumination, there is cross talk between the different separation channels defined by the capillaries. Due to the existence of scatter light, cross talk cannot be prevented and the contrast ratio of detected signals will be poor due to noise in the fluorescence emission. Furthermore, prior art single illumination source for multiple channels makes multi-wavelength LIF detection more complicated.
It is therefore desirable to develop a low-cost high throughput multi-channel detection scheme for bio-separation, which would overcome the limitations in the prior art.
The present invention provides a simplified, low cost, efficient, highly sensitive, and high throughput multi-channel detection configuration for bio-separation (e.g., CE), which overcomes the drawback of the prior art. The present invention provides a multi-channel detection scheme based on a multi-radiation source/common detector configuration, in which detection is conducted in a time-staggered, and/or time-multiplexed detection for the channels. A single detector is coupled to a plurality of radiation sources, in a one detector/many radiation sources configuration. Each radiation source directs radiation at one detection zone of a single separation channel, and a single detector is applied to detect light emissions from the detection zones of several separation channels. There may be more than one detector in the entire detection system, each serving multiple radiation sources.
Bio-separation may be conducted simultaneously in all the channels in parallel, with detection time-staggered and/or time-multiplexed with respect to the light sources. The light sources direct radiation at the detection zones in a predetermined sequence in a cyclic manner, with the detector output synchronized to the light sources by a controller. The radiation sources and the detector are pulsed in synchronization in a time-multiplexed manner. The controller controls the detector and radiation sources in a manner to effect detection of radiation emissions from the multiple separation channels in predetermined detection cycles, wherein each detection cycle is repeated at a frequency to provide a desired detection time or duration. The controller controls the radiation sources and detector in a manner to effect detection in a repeated scanning manner, across the detection zones of the separation channels, in a time-staggered type detection. In accordance with the present invention, cross talk between channels is virtually eliminated. No moving parts are required for directing the light source or detection.
In one embodiment, low cost light emitting diodes (LEDs) (e.g., super bright LEDs) or laser diodes, instead of expensive high power lasers may be used as light sources. Alternatively, low energy lasers may be used. The incident light from the light sources may be separately directed to the detection multi-channel detection zones using optic fibers. The emitted light from the multi-channel detection zones may be directed to one or more common detectors using optic fibers. Since no moving parts are necessary, component count can be reduced. By eliminating or reducing cross talk between channels, the optical detection system design can be much simplified. Accordingly, the cost, reliability, and ease of use of the instrument is improved.
In a particular embodiment of the present invention, the detection scheme of the present invention is configured for radiation induced fluorescence detection in a multi-channel bio-separation instrument. In another embodiment, the detection scheme is configured for radiation induced fluorescence detection in a capillary electrophoresis instrument.
In a further aspect of the present invention, multi-color incident radiation detection schemes may be applied to a single separation channel, in a time-multiplexed manner.
In another aspect of the present invention, the present invention provides a bio-separation instrument that incorporates the detection scheme of the present invention.
For a fuller understanding of the nature and advantages of the invention, as well as the preferred mode of use, reference should be made to the following detailed description read in conjunction with the accompanying drawings. In the following drawings, like reference numerals designate like or similar parts throughout the drawings.
This invention is described below in reference to various embodiments with reference to the figures. While this invention is described in terms of the best mode for achieving this invention's objectives, it will be appreciated by those skilled in the art that variations may be accomplished in view of these teachings without deviating from the spirit or scope of the invention.
The present invention is directed to a novel detection configuration in which multiple light sources emit excitation light through respective optical fiber toward respective fluid sample in a plurality of fluid samples in a time-multiplexed manner; fluorescence is generated in each of the fluid samples in response to the excitation light at different times corresponding to the times at which the light is transmitted to the samples; and the fluorescence from a single sample is delivered to the detector, which outputs a signal proportional to the intensity of the detected fluorescent light. Therefore, a single detector is used to detect light from a plurality of light emitting devices. For purpose of illustrating the principles of the present invention and not limitation, the present invention is described by reference to embodiments directed to CE, radiation induced fluorescence, and multiple separation channels. It is understood that the scope of the present invention is not limited to detection of fluorescence type of emission, but is also applicable to detection of other types of emissive radiation, such as phosphorescence, luminescence and chemiluminescence.
The mechanism of electrophoresis and radiation induced fluorescence when considered alone are outside the scope of the present invention. For the sake of completeness, it is sufficient to briefly describe CE in reference to the multi-channel CE system 200 in reference to FIG. 1 and FIG. 2. As shown in
In operation, a prepared biological sample (e.g., a DNA sample) is introduced into the far end of the capillary column 140 away from the detection zone 406, by any of a number of ways that is not part of the present invention (e.g., electrokinetic injection from a sample reservoir or physical pressure injection using a syringe pump). The sample binds to the fluorophore. When a DC potential is applied between electrodes 111 and 112, the sample migrates under the applied electric potential along the separation channel and separates into bands of sample components. The extent of separation and distance moved along the separation channel depends on a number of factors, such as migration mobility of the sample components, the mass and size or length of the sample components, and the separation support medium. The driving forces in the separation channel for the separation of samples could be electrophoretic, pressure, or electro-osmotic flow (EOF) means.
When the sample reaches the detection zone 406, excitation radiation is directed from light source 420 via the excitation fiber 422 at the detection zone. The sample components would fluoresce with intensities proportional to the concentrations of the respective sample components (proportional to the amount of fluorescent tag material). The detection fiber 428 collects the emitted fluorescence, at a wavelength different from that of the incident radiation and direct to a detector 450.
In one embodiment of the invention, referring to
The cartridge 100 includes a twelve-channel fused silica capillary array that is used for separation and detection of the samples as part of a disposable and/or portable, interchangeable cartridge assembly 100. The multi-channel capillary array includes twelve detection zones defined by micro-channels in the cartridge 100. The multi-channel cartridge 100 shown in
During electrophoresis, the rate at which the separated components or analytes move through the sieving gel is inversely proportional to their mass. As the fragments approach the detection zone 406, the excitation light energy from each of the twelve LEDs 420 supported in a LED module 433 is delivered by individual light transmitting optical fibers 422 (e.g., grouped in a bundle 423) to illuminate the separated components or analytes at the detection zone 406. The excitation light is delivered to the corresponding 12-capillaries directly with or without use of micro-lenses. The excitation fibers 422 may be coupled to each LED 420 by a micro-lens to improve optical coupling between the LEDs and the fibers. The fibers 422 are supported and aligned with respect to the capillary by a mount module or block 431. As the separated components or analytes move through the sieving gel (or linear polymer solution), an intercalating dye (Ethidium Bromide) within the sieving gel allows the separated components or analytes to be detected by detecting the light induced fluorescence.
The emitted fluorescent light from the capillary's detection zone 406 is then collected by several high N.A. (Numerical Aperture) micro-lenses 436 (e.g., High-index Sapphire Micro-lens) supported and aligned in the fiber mount block 431. The collected fluorescent light, which has a higher wavelength (large stoke shift) than the excitation light, is then routed by 12 larger core optical fibers 428 (370 μm OD, 0.22 NA fibers, but could also be in ranges of: 100-1000 um OD, 0.12-0.5 NA) from each of the 12 capillary's detection zone 406 and is brought into a single detector 450 (R5984 Hamamatsu photomultiplier tube) as a single bifurcated bundle assembly 452. A single, e.g., 570-630 nm long pass optical filter 454 (OG-590) is used prior to detection to filter the emission signal from the output of the fiber bundle (each fiber) assembly 428.
The LEDs 420 are operated to emit light at different times (i.e., modulated). Hence, light from only one LED 420 from LED module 433 is delivered to single capillary 140 at any given time and is detected by the detector 450, which outputs a signal proportional to the intensity of the detected fluorescent emission. Light induced fluorescence detection is proceeded in a predetermine sequence and in a cyclic fashion for all the detection zones 406 at capillaries 140, in synchronization with the activations of the LEDs 420. Therefore, a single detector 450 is used to detect fluorescence emissions from a plurality of radiation emitting devices.
The twelve LEDs 420 are pulsed/modulated in a time-multiplexed manner with respect to the detector. The LEDs are pulsed, and similarly the detector is pulsed also. The detector just reads one LED or one channel at a time in a time-staggered manner. As the LEDs are pulsed and continuously exciting the fluorophor which is tagged with the separated DNA fragments through all channels running in parallel, the detector is also sampling or reading one channel at a time in a time-staggered manner. In essence, detection is conducted in a repeated scanning manner, across the detection zones of the array of capillaries 140. Twelve emission signals will reach the single PMT 450 (photo-multiplier tube) in a time-staggered manner by a single fiber-bundle assembly or they could be individual emission collection fibers which are all combined to a single detector. These detection fibers do not need to be in a 1�12 fiber bundle assembly form. They could be 12 individual fibers which are mounted individually to a single detector module by a single mechanical block, so they could either be packaged either in a 12 closed round packed or linear array packed form, delivering total of 12 emission signals from the cartridge to a single PMT. The light emitting diodes 420 are operated to emit light pulsed at several hundred hertz but separated from each other by a delay.
In general, pulsing of the LEDs are conducted in the following sequence in accordance with one embodiment of the present invention. When LED one comes on then detector comes on or detects emission light for LED number one, then LED one becomes off for the next 11 times because there are a total of 12 channels. So the pulsing of the LEDs is tied to the detector which is done in a sample and hold scheme. The sampling frequency may be 100 Hz per channel so the total modulation frequency for all 12 channels is 1200 Hz, which is the frequency for the two consecutive channels, with a duty cycle of {fraction (1/12)}. This sampling frequency may be different as long as the time-multiplexing of LEDs and the time-staggered type detection scheme is preserved. The data collection processing rate in the software may be set at 10 Hz with an adjustable rise time (i.e. 0.1 sec-1 sec). (To have the similar sampling frequency, a sampling frequency of 10 Hz instead of 100 Hz may be used, but sampling frequency and data collection processing rate are independent from each other.) Then the LED would be on for about 10 msec and off for 100 msec at {fraction (1/12)} duty cycle. (This duty cycle will change as the number of capillaries increases or decreases).
As can be seen in
It is noted that electrophoretic separations of fragments in the CE instrument 200 in accordance with the present invention are in seconds versus milliseconds for the pulsed LED on time. Because the pulsing frequency is much higher than the actual fragment peak separations, the time staggered/time multiplex detection scheme of the present invention does not negatively affect the sensitivity and performance of detection resolution. The resolution of the detection results (e.g., peaks in the detected signal) would depend in part on the gel matrix concentration, the separation inner diameter, length and the speed of migration through the detection zone 406. Experiments have shown that detection sensitivities of 100 ng/ml (0.02 ng of the DNA fragment) could be achieved with good resolution using the inventive detection scheme.
As an example, for a test sample comprising ΦX174 DNA fragment, with 75 μm by 16 cm capillary at 300 V/cm electrical potential, a baseline resolution for the 271/281 base pairs can be achieved. The STR loci in an individual DNA Identification type separations with standard markers show about a 4 base pair separation resolution using the a single color time-multiplexed fluorescence detection approach in accordance with one embodiment of the present invention. Separation time for all 12 channels running in parallel is less than 10 minutes with a good Signal-to-Noise ratio (S/N=150 for the largest fragment, based on peak-to-peak noise).
The pulsing of the radiation sources and the detection sampling rate and period should be synchronized so that the desired detection for a channel covers a period when only the associated radiation source is on with respect to the detector.
While the above described embodiment shows the source LEDs directing incident light to the capillaries via optic fibers 422, it is within the scope and spirit of the present invention to position the radiation sources, such as the LEDs, adjacent the detection zone 406, using short optic fiber alignment leads 427 to align incident light to the detection zone or completely eliminating use of fiber optics (e.g., by deploying micro-lenses to align incident light from LEDs directly to the capillary detection zone 406).
In a preferred embodiment, as shown in
The components of the controller 300, with the exception of the PC 218, may be packaged as an electronic board 64 (
Incident radiation for the detection may be directed at the detection zone and/or radiation emissions from the detection zone may be output axially along the separation medium (references are made to U.S. patent application Ser. No. 09/887,871 entitled Optical Detection in Bio-Separation Device Using Axial Radiation Input; U.S. patent application Ser. No. 09/887,953 entitled Optical Detection in Bio-Separation Device Using Axial Radiation Output, and U.S. patent application Ser. No. 09/887,872 entitled Optical Detection in Bio-Separation Device Using a Widened Detection Zone, all filed on Jun. 22, 2001, which are commonly assigned to BioCal Technology, Inc., the assignee of the present invention, and which are fully incorporated by reference herein.
The present invention utilizes low cost and miniature LEDs as excitation sources. Other non-coherent, broadband light sources could be used (i.e., xenon lamps, D2 lamps, mercury lamps, arc lamps). The emissions from the detection zone are collected by micro-optical lenses with fiber delivery systems either from outside or inside the detection collar.
Super-bright LEDs (i.e. Agilent's InGaN LEDs in colors of blue, green, etc . . . ) are candidates for inexpensive, compact, low-power light sources for use in the detection scheme of the present invention. These super-bright LEDs based on InGaN material technology (HLMP-CB15 and HLMP-CM15 from Agilent) have an average light output power of 2.5-3 mW. The spectral characteristics of these blue-green InGaN LEDs with their Peak Wavelengths of 470 and 530 nm and halfwidths (nm) of 30 to 50 nm are good candidates to be used for excitation of dyes (e.g. fluorescin, rhodamine, Etidium Bromide, thiazol orange), with excitation spectra in the range of 450 to 550 nm. Any solid state light source that can be pulsed could also be used with any dye or fluorophor for this type of time-multiplexed detection. Since the response time of these LEDs are very high (few hundred nanoseconds in frequency ranges of 1 Hz-to-100 MHz), they could be pulsed at greater forward currents (e.g., 15-30 mA, but could be up to 100 mA forward current in pulsed mode operation), to obtain high radiant peaks. Pulsed operation of LEDs can typically be achieved by the transistor drive circuits. Significantly higher peak LED light output can be realized from large drive current pulses at lower duty cycles than DC operation. Another example is LED-array module consisting of Green 524 nm LEDs, which can also be adopted as excitation light sources for the fluorescence detection of a low-cost CE instrument.
The innovative detection approach has many advantages over the existing commercial CE instruments. The detection system utilizes inexpensive light emitting diodes (LEDs) as excitation light sources for fluorescence type detection. The attractive features of LEDs as light sources are their low cost, small size, long lifetimes, good intensity stability resulting in low noise, and the possibility of direct electronic modulation. These smaller solid-state excitation light sources facilitate the fiber coupling, which results in miniaturization of the detection optics. Using a time-staggered detection approach by multiplexing of multi-LEDs provides a great advantage of reducing number of detectors (e.g., PMTs) to possibly one for multi-channel detection. By reduced component count and by simplifying the optical detection system design the cost, reliability and ease of use of the instrument is improved. There are negligible or no cross talks between separation channels.
While in the embodiments described above, the multiple radiation sources are at the same wavelength, it is within the scope and spirit of the present invention to configure the multiple radiation sources at different wavelengths, to complement the specific samples, sample based detection applications or gel chemistries in the different capillaries. For example, adjacent radiation sources may have alternating wavelengths, to run separations with identical samples in two adjacent capillaries with different gel chemistries and/or fluorescence tags, to allow comparison of the detection results for determining different or additional separated components in the sample, or as a basis of validation of the detection results. As another example, adjacent group of four capillaries may be incident with radiations of four different wavelengths (thus in the 12-channel system described above, there would be three groups of four channels) for the same sample. The same may be applied for detection of emissions from the channels incident with radiation of the same wavelength, in a time staggered and/or time multiplexed manner described above. Alternatively, there are multiple detectors, of same or different performance and/or detection characteristics, each applied for detection of emissions from the channels incident with radiations at the same wavelength in a time staggered and/or time multiplexed manner described above. Other variations are within the scope and spirit of the present invention.
Referring to
Referring to
Incident radiation is directed by optic fibers 210 and 212, which are supported and aligned by V-grooves 204 as shown. In the embodiment shown, the fiber 210 and 212 are aligned in-line, across the detection zone of the capillary 140. Radiation sources such as two LEDs 216 and 218 at different radiation wavelengths provide the incident radiations, each LED being coupled to one of the fibers 210 and 212.
Optic fibers 220 and 222 direct radiation (e.g., emitted radiation from radiation induced fluorescence) from the detection zone. The ends of the optic fibers 220 and 222 at the detection zone is supported by a ferrule 224 and 225, and provided with micro-ball lenses 226 and 227 having the appropriate numerical aperture to capture the emitted radiation from the detection zone. The ferrules 224 and 225 along with the ball lenses 226 and 227 are inserted into the through-hole 214 in the alignment block 201, thus supported and aligned with the detection zone.
The fibers 220 and 222 directs emitted radiation from the detection zone to one or more detectors, such as a PMT detector 228, via a fiber array connector 229 and emission filters 230 and 232, which may be at different wavelengths. The different emission filters detect or distinguish two different wavelengths using the single PMT. The time multiplexing or time-staggered type detection allows use of a single PMT with multi-color excitation light sources, and this differentiates the two emission signals. There may be stray light or wavelength overlaps between two LEDs, but this could be solved by appropriate selection of emission filter and design.
Controller system 301 in
The cartridge 250 may be adapted to be supported in a laboratory robotic system, such as the system described in connection with
In operation, the LEDs 216 and 218 are multiplexed with respect to the detector 228. The LED scan board 234 and other associated control elements control the LEDs 216 and 218 and the detector 228 in a manner such that the radiation from each of the LEDs is introduced at the detection zone in a predetermined sequence and radiation emission from the detection zone is detected in a time staggered/multiplexed manner, similar to the process describe in the earlier embodiments. The difference between the current embodiment and the earlier embodiments is that multiple radiation sources are directed at a single separation channel, compared to the earlier embodiments in which each separation channel is coupled to one radiation source. Nonetheless, the time staggered/multiplexed process is equally applicable here. Similar design considerations associated with pulsing of radiation sources, sampling rate and period, lag time, repetitive detection cycle, detection resolution, scanning of radiation sources, etc. are adopted for multiplexing multiple radiation sources with respect to a single detector. Further, in the event there are multiple separation channels, each applying multiple radiation sources, all the radiation sources may be time staggered/multiplexed with respect to emitted radiation detection in a similar manner.
The cartridge top reservoir 254 is pre-filled with gel prior to start of separation run (e.g., pre-filled at factory assembly prior to shipment). The reservoir 254 contained with gel is sealed air-tight. There is a rubber septum 260 at the wall of the cartridge reservoir 254, which provides an access to the gel reservoir 254. By poking through the septum 260 using a needle/syringe, gel could be filled inside the cartridge's reservoir. At the instrument side where the cartridge gets engaged with an interface plate (not shown), a sharp needle 262, which is coupled to the air pressure syringe pump 78 (FIG. 7), pokes through the septum 260. This approach assures the proper containment of the gel inside the cartridge reservoir 254 and provides a simple yet reliable means of accessing the gel reservoir 254 from outside to provide enough air pressure to the reservoir to fill up the capillary 140 prior to high voltage separation.
There are multiple excitation light sources (e.g., two different color LEDs, e.g., at 473 nm and 535 nm). Each LED's broad-band light energy (FWHM=35-50 nm) is coupled in-to-individual fibers (Multimode step-index silica fibers, 0.22 N.A.) and are delivered to the capillary detection zone from port defined by the V-grooves in the alignment block 201.
In a four color LED configuration, two additional LEDs (e.g., at 570 nm and 630 nm) are provided from two additional ports defined by the V-grooves in the alignment block 201.
The emitted fluorescent radiation is then collected by several high N.A micro-lenses (micro-optical elements) with attached fiber pigtails from each of the two (in the case of a two-color configuration) or four (in the case of a four-color configuration) planes or quadrants of the capillary's detection zone. The collected emission signals are routed by 2 or 4-individual Step-index, large core fibers from capillary detection zone to a single Detector (photomultiplier tube) after going through 2 or 4-color separation using 2 or 4-emission color filters. The LEDs are operated to emit light at different times in synchronization in a time staggered/multiplexed mode. Hence, light from a single color LED (emitter) is delivered to the capillary at any given time (i.e., each LED comes on at different time) and is detected by a single detector, which outputs a signal proportional to the intensity of the detected 2 or 4-fluorescent signals. Therefore, a single detector is used to detect light from a plurality of light emitting (multi-color) light sources.
Current Multi-color Capillary Electrophoresis instruments employ costly and bulky single or multiple Laser light sources as an excitation source. In the inventive device, low-cost and miniature LEDs are used as excitation sources for each of the fluorophores. The light from multi-color LED excitation sources are coupled into individual optical fibers and are brought into close proximity/side of a single capillary/micro-channel (flow cell). The emission signals are collected by micro-optical lenses with fiber delivery systems and are brought into a single detector (PMT). The LEDs are time-multiplexed for each color (excitation wavelengths) and the emitted Fluorescence signals from single or multiple capillaries are collected by emission fibers and are delivered to a single detector (PMT) in a time-multiplexed fashion and the wavelengths are separated by emission filters. By reduced component count and by simplifying the optical detection system design the cost, reliability and ease of use of the instrument is improved.
The present invention provides a low cost and a fixed micro-optical (non-moving mechanism) scanning apparatus (electronically scanning) comprising plurality of multi-color (wavelength) light emitting devices, such as light emitting diodes, which each of the LEDs (or lasers, or other radiation sources) emit excitation light of different color through a respective optical fiber toward a respective fluid sample in a time-staggered manner. Therefore, multiple fluorescence signals (emission light) are generated from a single fluid sample with multiple fluorophores in response to the multi-excitation light sources at different times corresponding to the times at which each of the colors are delivered to the sample. Fluorescence spectroscopy is used for our multi-color detection because among instrumental techniques, fluorescence spectroscopy is recognized as one of the more sensitive. In fluorescence, the intensity of the emission of the sample is measured. The reason for the high sensitivity of fluorescence techniques is that the emission signal is measured above a low background level. This is inherently more sensitive than comparing two relatively large signals, as in absorption spectroscopy. Fluorescence techniques are as much as 1000 times more sensitive than absorption spectroscopy.
The present invention also provides a portable, real-time multi-color fluorescent detection of STR alleles as a sensitive, low-cost and accurate approach for DNA typing (Human Identification through DNA analysis). STRs are highly applicable for genotyping testing because the loci are highly polymorphic and alleles can be identified from degraded DNA. Single-channel capillary electrophoresis device with a multi-wavelength LED-based Induced Fluorescence detection system can be used for the fast analysis of an eight-loci, two-color multiplex short tandem repeat (STR) system for human identification. Polymorphic STR loci are extremely useful markers for human Identification, paternity testing and genetic mapping. STR loci consist of short, repetitive sequence elements of 3 to 7 base pairs in length. STR loci may be amplified via the polymerase chain reaction (PCR) by employing specific primer sequences identified in the regions flanking the tandem repeat. Alleles of these loci are differentiated by number of copies of the repeat sequence contained within the amplified region and are distinguished from one another following electrophoretic separation by any suitable detection method (in our case fluorescence type detection). Fluorescent labels used to label each such primer is preferably a fluorescine label, ethidium bromide or tretramethyl rhodamine label. Most preferably, at least two different labels are used to label the different primers, which are used in the multiplex amplification reaction. One such example for DNA Typing is PowerPlex 16 System from Promega (U.S. Pat. No. 5,843,660).
The present invention for the detection mechanism and the single channel cartridge could be configured in a small portable package and applied as a field portable personal identification (DNA ID) type device. By having a build in PCR device in combination with a multi-color CE detector the final instrument becomes a simple DNA identification tool for courts and remote stations. By having multi-color versatility in which multiplexing of LEDs enables the detection of a wide variety of fluorescent dyes. This allows you to perform multi-color applications, such as SNP genotyping, multiplexed quantitation. Dual or multi-color detection features, with the use of internal standards, allows greater reassurance about amplification efficiency of PCR DNA. Polymerase chain reaction (PCR): is a technique in which cycles of denaturation, annealing with primer, and extension with DNA polymerase are used to amplify the number of copies of a target DNA sequence by approximately 106 times or more. The polymerase chain reaction process for amplifying nucleic acid is covered by U.S. Pat. Nos. 4,683,195 and 4,683,202. One of the most important pieces of equipment necessary for PCR is the thermal cycler. PCR instrumentation has developed from heat control blocks to rapid thermal cycling for heating and cooling of nucleic acid and enzyme reaction mixtures, so enabling DNA denaturation, reannealing and extension.
The following are steps for an example of a process of individual identification using a portable DNA ID device:
There can be many commercial applications of the portable instrument. Molecular biologists and chemists can use the portable analytical instrument in research labs or in many remote locations (such as crime scenes, courts, hospitals, military facilities, inside police/patrol cars and other locations requiring portability of the instrucment) for individual identification, forensic applications, biological warfare (viral or bacterial) detection, food and water quality monitoring, environmental sensing, cancer detection and other types of disease detection. The portable analytical device is preliminary designed for DNA analysis. Forensic researcher can use the portable device for DNA base individual identification type testing. And also with alternative cartridges the instrument can be used for other type of analysis (i.e. proteins).
While the invention has been particularly shown and described with reference to the preferred embodiments, it will be understood by those skilled in the art that various changes in form and detail may be made without departing from the spirit, scope, and teaching of the invention. For example, the excitation radiation source could be, for example, LEDs, laser diodes (semiconductor solid-state lasers), pulsed lasers (e.g., solid state lasers, gas lasers, dye lasers, fiber lasers), or other sources of radiation. LEDs (e.g., Green, 524 nm) are associated with low cost, super brightness, and small package. Alternate relative inexpensive light source for the present invention could be laser diodes in the visible, UV and/or infrared range. For example, laser diodes in the range of 400-900 nm, and more specifically in the range of 400-600 nm may be used, for example.
A person skilled in the art will recognize that the instrument incorporating the essence of this invention can also be used for biomoleculer analysis other than DNA analysis. For example, by altering the separation gel or buffer, the system can also be modified to analyze biomolecules like proteins, carbohydrates, and lipids.
By way of example and not limitation, the detection scheme of the present invention is described in connection with CE and radiation induced fluorescence detection. It is understood that the present invention is also applicable to detection of analytes separated based on bio-separation phenomenon other than electrophoresis, and detection of radiation emissions other than fluorescence emissions. The same principle of multi-color could be applied for an absorbance type detector applying the time-multiplexing detection technique.
Accordingly, the disclosed invention is to be considered merely as illustrative and limited in scope only as specified in the appended claims.
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text: blog postsCalendar XMLJan 17, 2011 11:45 am by email@example.com The calendar XML schema is below: http://illinois.edu/calendar/calendarws.xsdBelow is an example of how to query for XML data (replace the 7 with your calendar ID):http://illinois.edu/calendar/eventXML/7.xmlHow often will this schema change?The schema used to extract event data is not the same schema we use to display the calendar. We have a hidden schema that contains many more fields that relate specifically to display data. We created two separate schemas so that as we make changes to how the calendar looks we won't impact those groups consuming our data. Since this schema only contains the necessary data for events we do not anticipate changes being made.More specific queriesUsing the "search" tab from the public calendar web interface you will notice that there are many web parameters used when searching. searchEventType KEYWORDS startDate endDate Below is an example of searching based on a start date and end date. You will notice that the slash that separates the elements of a date are HTML escaped with %2F. You will also notice that the month and day are always two numbers: http://illinois.edu/calendar/eventXML/7.xml?startDate=07%2F01%2F2015&endDate=07%2F23%2F2015 Any of these parameters can be added to the web query "/calendar/eventXML/#.xml" in order to filter the results. The web parameter "searchEventType" can be used more than once. How to specify date ranges in a web query Generating events, like all data processing, has CPU, memory and other types of costs associated with it. So in order to provide reasonable services we only provide up to 100 events per query. The recommended strategy for getting events is to: Query based on a date range. Most people query all events within a month. If you find that there are less than 100 events then you have the whole month. Else do one query for each week in the month. If you find that any particular week contains 100 queries then do one query for each day within that particular week. Appropriate Use of Services Requests to our server for data are limited to twice per day maximum. XML data should be stored on your servers. Misuse of these privileges can result in loss of access to these services. If you have a special case, please let us know. In many cases we are able to supply widgets that will do what you need. Just make a request. Our support for this service is M-F during regular business hours. stats617 Views 0 Comments additional actions


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Pulau Semakau Things to Do Tips by bpacker
Pulau Semakau Things to Do: 6 reviews and 10 photos
Most RecentBest Rated
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Chinese Egret? Pulau Semakau
Birding is another activity that you can do in Pulau Semakau. The remoteness of this place somehow attracts a rich diversity of rare birds that can't be seen on the mainland. So if you're hear on a birding trip, bring a pair of binoculars with you. The one that is given free on National Day does not count as one. Do check out my off the beaten page to see what birds can be seen.
Non-refundable $25 fee for boat and administration. Do note that this trip is only open for Nature Society members. Click the website for details on how to join the Nature Society.
This little sotong (squid) is so cute that I've decided to put it here. It was spotted off the sea-grass lagoon in Pulau Semakau that day and oohed and ahhed by everyone in the group. Of course, it was released into the water after the trauma.
Other birding your brains out, angling and wading the waters in Pulau Semakau, you can also check out the unusual mangrove trees by the shore. Many of these trees have stilt roots that poke eerily out the water for air. Many of these trees attract birds and mudskippers so it pays to hover near them.
Inter-tidal walk at semakau
Honestly, the best thing about going to Pulau Semakau is to check out what nature has to offer. Going for an inter-tidal walk ( walking along the shore when the tide is low) with a guide would be good idea as you'll appreciate what you see with understanding. And please remember, bring only the memories and photographs home. For pete's sake, don't bring a bucket to collect mussels for dinner, it's not only illegal but detrimental to nature*. Check out the website below for the schedule of the walks.
Students: $39.90 per person
Public: $52.50 per person
Cost includes rental of boat, guides, guidesheets, coordinating and administrative fees.
Group Size
1 guide and 1 trainee guide to 10 participants.
*I'm not joking, I actually spotted an old woman clutching a red bucket, harvesting shell fish "gong gong" at Pulau Ubin. What she didn't know was that this action is ILLEGAL in a nature reserve. Plus, Singapore waters ain't exactly clean so after eating the shellfish, you might end up ***ting your insides and puking your brains out.
Website: http://rmbr.nus.edu.sg/workshop/
Fishing in Pulau Semakau
Besides the walks and birding activities, sport fishing is another activity you can do in Pulau Semakau. It's quite a worth while activity since I was told that black-tipped sharks were seen swimming in the lagoon and LARGE groupers were actually caught in these waters. Ah, sounds tempting doesn't it? Now to pour cold water over what I said, you'll need to release any fish caught in these waters. Yes, you're NOT ALLOWED to bring back any fish caught from this waters. Are you still keen, if you are, click on the website for the price and other details.
Members- $30 per trip
non-members - $40 per trip covering ferry transport and admin costs.
Bring your own food, drinks, fishing tackle, rain gear etc.
Website: http://www.sfas.net./
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Reviews written
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|One Liner
|Review Date
|Die Hard Arcade
|SEGA Saturn
|""Yippie-Ki-Yay Mr. Sociester!"-From TV edit of Die Hard-"
|Sep 05, 2007
|The House of the Dead
|SEGA Saturn
|"Not by Dostoevsky….."
|Oct 27, 2009
|Albert Odyssey: Legend of Eldean
|SEGA Saturn
|"Do You Have Albert Odyssey In A Can? "
|Oct 12, 2007
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|SEGA Saturn
|"The End Of The Saga"
|Aug 03, 2008
|Virtua Cop 2
|SEGA Saturn
|"Walk Softly And Carry A Big Gun"
|Oct 04, 2008
|Shining Force III
|SEGA Saturn
|"Quite Possibly The Best Game In The Series."
|Feb 29, 2008
|Shining the Holy Ark
|SEGA Saturn
|"Shine On You Crazy Diamond"
|Jan 27, 2009
|Chrono Trigger
|"Gotta Go Back In Time...."
|Sep 10, 2006
|The Adventures of Batman & Robin
|"The Dark Knight Returns"
|Nov 16, 2008
|Killer Instinct
|"This Game Should Be Buried In The Middle Of Nowhere And Never Be Spoken Of Again"
|Jun 08, 2007
|Final Fight
|"If only this was the final fight..."
|Apr 05, 2006
|Final Fight 2
|"I Thought The Last One Was The Final Fight...."
|Nov 10, 2006
|Batman Returns
|"Terrible Film. Fun Game."
|Jun 21, 2007
|Final Fight 3
|"What Is With The Developers, And Not Knowing What "Final" Means?"
|Nov 12, 2006
|Breath of Fire
|"Old Skool Is In Session"
|Dec 02, 2008
|Final Fantasy V
|"A Huge Step Back For The Series"
|Apr 16, 2009
|Mario's Tennis
|Virtual Boy
|"Nintendo's New Coke"
|Jul 14, 2009
|The House of the Dead: Overkill
|"Collect Your Point Blank Prescription! "
|Apr 24, 2010
|Super Mario Galaxy
|"WOPS, In Space!!!!!!!!!!!!!!!!!!!!!!!!!!!!!!!!!!!!"
|Jan 31, 2010
|Clive Barker's Undying
|"The Covenant Family Is Just Undying To Meet You!"
|Sep 18, 2006
|Sam & Max: Hit the Road
|"The Adventures Of A Shamus Canine And Hyperactive Rabbity Thing"
|Apr 13, 2009
|Sam & Max: Episode 2 - Situation: Comedy
|""You Crack Me Up Little Buddy."-Sam, The Bipedal Dog-"
|Jan 22, 2007
|Sam & Max: Episode 3 - The Mole, the Mob, and the Meatball
|"An Offer You Can't Refuse"
|Aug 05, 2007
|Serious Sam: Gold
|"Are you Serious?"
|May 07, 2006
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|"Who's Up For A Round Of NOLFING?"
|Aug 11, 2006


text: As Im a beginner in the world of the video games and before this have never played any games. So I would like to know is there any beginner in the rocksmith game and what are your views and opinions regarding this game. As I would like playing this game and am much awaited for this game to get released for the PC. So I would like your views and opnions from the beginners for the rocksmith game.


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How to Jib
Jibbing is a basic to complicated trick in snowboarding. It can involve almost any obstacle, i.e. barrel, trees, kids.
This article has been tagged as a stub.
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1Make sure you have the knowledge and ability to jib especially if it's your first time.
2Scope out the object you wish to jib. Make sure it's clear of any obstacles, except the ones you're jumping over. If you're jumping over people, make sure they're aware.
3Make any necessary adjustments. Make a little lip in the snow move a rock or something break off a branch
4Approach with what you want to do in mind. A 270 Tail Tap, a 180 Nose Bonk, or just do a normal jump. It doesn't effect the jib. Just make sure you know you can do the trick.
5Ollie up, keep your balance,and ride away clean.
6Next time you jib try to add style.
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Ask a Question
- Be careful.
- Stay calm.
- Make sure you are an expert level snowboarder before attempting this trick.
Things You'll Need
- snowboard
- Air-blaster
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