Al 1000

Manufactured by World Precision Instruments

Sourced in United States

The AL-1000 is a lab equipment product designed for general laboratory use. It serves as a core function without further interpretation or extrapolation on its intended use.

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Lab products found in correlation

Dm il led, by Leica (1 mentions) Pc 420d, by Corning (1 mentions) Dionex ultimate 3000 uhplc system, by Thermo Fisher Scientific (1 mentions) Tsq vantage ms, by Thermo Fisher Scientific (1 mentions) Form 3b 3d printer, by Formlabs (1 mentions) Tygon tubing, by Cole-Parmer (1 mentions) Zoletil, by Virbac (1 mentions) 3 ml syringe, by BD (1 mentions) Calcein, by Merck Group (1 mentions) Polytetrafluoroethylene ptfe tubing, by Cole-Parmer (1 mentions)

Close spelling variants of this product

Aladdin AL-1000 (3 citations) AL 1000-220 (3 citations) AL-1000 syringe pump (2 citations)

19 protocols using al 1000

Measuring PDMS-PS Bonding Strength

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To evaluate PDMS/PS bonding strength, a PDMS-based microfluidic layer with a long square microchannel (100 μm × 100 μm) was fabricated and placed on a PS surface, followed by applying gentle pressure for removing any air between the surfaces. Then, water containing a red dye (for better visualization) was injected into the microfluidic channel at a rate of 1 μL min⁻¹ using an accurate syringe pump (AL-1000, World Precision Instruments, USA). Fluid flow was monitored under an inverted microscope (Leica DM IL LED) and the length of the microchannel filled with the fluid immediately before leakage was measured. Bonding strength was calculated using the following equation²⁵:

B o n d i n g S t r e n g t h = (28.4, η, L, q, h^{- 4}) + (- γ [\frac{3 cos θ_{PDMS} + cos θ_{PS}}{h}]) (1)

where the first term stands for the flow resistance in the microfluidic channel and the second term indicates the capillary pressure. In this equation,

η

L

q

h

and

γ

are dynamic viscosity of water, the filled length of the microchannel, flow rate, width or height of the microchannel and surface tension of the water. Also,

θ_{PDMS}

and

θ_{PS}

are water contact angles on PDMS and PS surfaces, respectively. The contact angles were measured to be ~ 110° and ~ 80° for PDMS and PS, respectively.

Samandari M., Rafiee L., Alipanah F., Sanati-Nezhad A, & Javanmard S.H. (2021). A simple, low cost and reusable microfluidic gradient strategy and its application in modeling cancer invasion. Scientific Reports, 11, 10310.

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Single Molecule Talin Pulling Experiments

Cited 2 times

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The single molecule talin pulling experiments were carried out using a set of high force vertical magnetic tweezers built in house. These tweezers allow for simultaneous force and extension measurements for short protein and DNA tethers16 (link)33 (link)34 (link). Laminar flow channels were constructed with a NTA-Cu2+ functionalized coverslip for specific talin immobilization as reported previously35 (link). Force was applied to the talin fragments by streptavidin coated magnetic beads (M270 streptavidin, Dynabeads). A syringe pump (AL-1000, World Precision Instrument) was used to control the flow rate of buffer switching (∼3 μL/min). The force of buffer flow is estimated at less than 1 pN. All talin pulling experiments were done in 1X PBS, 10 mM β-mercaptoethanol, 1 mM AEBSF and 10 mg/ml BSA at 22°C with various concentrations of Vd1.

Yao M., Goult B.T., Chen H., Cong P., Sheetz M.P, & Yan J. (2014). Mechanical activation of vinculin binding to talin locks talin in an unfolded conformation. Scientific Reports, 4, 4610.

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Coaxial-Electrospray Encapsulation of DTA Pectin and AXF-Ins

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A coaxial-electrospray Spraybase™ system (Profector™, Dublin, Ireland) and two programmable syringe pumps (WorldPrecision Instruments, AL-1000, Sarasota FL, USA), independently connected to the coaxial metallic needle (Figure 1), were used. In order to receive spraying droplets, a crosslinking solution was employed containing CaCl₂, water, and ethanol. Injection flow, applied voltage, and CaCl₂ and ethanol concentration in the crosslinking solution were varied for each experimental run according to experimental design described in Table 1.
The syringe from the outside of the needle contained DTA pectin, and the AXF-Ins solution was in the central section of the needle, along with 1.25 U/mL of laccase. One hundred μL of each polysaccharide solution were injected. The reception of the spray was performed in a volume of 10 mL of crosslinking solution with constant stirring at 200 rpm (Corning^®, PC-420D, Corning, NY, USA) during the manufacturing time and further stirring for 2 h as a gel curing period. Samples were stored at 4 °C.

Rascón-Chu A., Díaz-Baca J.A., Carvajal-Millan E., Pérez-López E., Hotchkiss A.T., González-Ríos H., Balandrán-Quintana R, & Campa-Mada A.C. (2018). Electrosprayed Core–Shell Composite Microbeads Based on Pectin-Arabinoxylans for Insulin Carrying: Aggregation and Size Dispersion Control. Polymers, 10(2), 108.

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Microneedle Fabrication via Spray Deposition

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A commercial coaxial needle (Ramé-hart instrument co., Succasunna, NJ, USA) was used as an atomizing spray nozzle. The outer needle (15 gauge) was connected to a compressed air source, and a solution was fed through the inner needle (21 gauge) by a syringe pump (AL-1000, World Precision Instrument, Sarasota, FL, USA). To fabricate PVP and PLGA microneedles using the spray deposition process, polymer solutions were prepared and sprayed with specific spraying parameters (Table 1) and dried for 15 min at room temperature. The same procedure was repeated five times to form microneedles. A backing layer composed of 40% w/v PVP (MW 40 kDa) and 2.5% v/v glycerol in deionized water was then applied to all the fabricated microneedles and dried overnight at room temperature.
Similarly, PLGA-PVP multilayer microneedles were fabricated by sequential deposition of PLGA and PVP solutions using the spraying parameters described in Table 1. PLGA solution was firstly sprayed onto the microneedle mold, dried for 15 min, and PVP solution was sprayed. To distinguish each layer, SRB and coumarin 314 were added to the aqueous PVP and organic PLGA solutions, respectively. The fabricated multilayer microneedles were visualized using an inverted fluorescence microscope (Olympus IX-73, Tokyo, Japan) coupled with a digital camera and integrated software.

Kim M.J., Park S.C., Rizal B., Guanes G., Baek S.K., Park J.H., Betz A.R, & Choi S.O. (2018). Fabrication of Circular Obelisk-Type Multilayer Microneedles Using Micro-Milling and Spray Deposition. Frontiers in Bioengineering and Biotechnology, 6, 54.

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UHPLC-MS Instrumentation for Analytical Research

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The Dionex UltiMate
3000 UHPLC system and the TSQ Vantage MS with the HESI-II ion source
were purchased from Thermo Fisher Scientific. A syringe pump (AL-1000)
was bought from World Precision Instruments (Sarasota, FL). A 2-position
10-port valve (for 1/32″, C82X-6670ED) was purchased from VICI
Valco. A SUB Aqua 5 Plus water bath was purchased from Grant Instruments
(Cambridge, U.K.). A Form 3B 3D printer and wash and cure station
were purchased from Formlabs Inc (Somerville, MA). A PST-BPH-15 column
heater was purchased from MS Wil (Aarle-Rixtel, the Netherlands).
A refrigerated circulating water bath was purchased from Haake (Berlin,
Germany).

Kogler S., Aizenshtadt A., Harrison S., Skottvoll F.S., Berg H.E., Abadpour S., Scholz H., Sullivan G., Thiede B., Lundanes E., Bogen I.L., Krauss S., Røberg-Larsen H, & Wilson S.R. (2022). “Organ-in-a-Column” Coupled On-line with Liquid Chromatography-Mass Spectrometry. Analytical Chemistry, 94(50), 17677-17684.

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Immobilized Enzyme Kinetics Monitoring

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From a stock solution of DCFH₂-DA (5 mM in DMSO) and a diluted stock solution of H₂O₂ (0.9 mM in PB, prepared from a 2 M H₂O₂ stock solution in water) a solution containing 50 μM DCFH₂-DA and 9 μM H₂O₂ was freshly prepared in PB (pH = 7.2, 1 vol% DMSO). This substrate solution was passed through the filter holder at 5 μL min⁻¹ for 180 min by using a syringe pump (AL1000 from World Precision Instruments). The outflow was collected in 1.5 mL polypropylene tubes, using a new, empty tube every 30 min. The absorption spectra of the collected outflows were measured with a spectrophotometer (quartz glass cell, l = 1 cm, background: PB). The performance of the immobilised enzymes was evaluated by plotting A₅₀₃ as a function of time, yielding approximate values for the concentration of DCF, using ε₅₀₃ (DCF) = 101 900 M⁻¹ cm⁻¹ (see Fig. S-3, ESI†). For the collected final outflow (t = 150–180 min), the full absorption spectrum was analysed with the analytical methods already applied for the cascade reactions in bulk solution, as described in “Results and discussion” (Section 3.1.6.).

Ghéczy N., Sasaki K., Yoshimoto M., Pour-Esmaeil S., Kröger M., Stano P, & Walde P. (2020). A two-enzyme cascade reaction consisting of two reaction pathways. Studies in bulk solution for understanding the performance of a flow-through device with immobilised enzymes. RSC Advances, 10(32), 18655-18676.

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Microfluidic Device Fabrication Protocol

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The microfluidic device was fabricated using the conventional approach of photo- and soft-lithography as described previously.⁵⁰ Briefly, the master mold was fabricated by patterning SU-8 photoresist on a silicon wafer. Subsequently, the microchannels were formed by molding Sylgard 184 reagents, according to the manufacturer's instructions (Dow Corning, USA). A 10 : 1 mixture of base and curing agent was poured on the master, degassed and baked for 30 min at 80 °C on a hot plate (RH digital, IKA, Germany). The cured elastomer was then peeled, punched to open the desired inlets and outlets and cleaned with adhesive tapes. The microchannels were then sealed by bonding the polydimethylsiloxane (PDMS) substrate to a glass microscope slide using the plasma activation (BD-20AC, Electro-technic Products, USA). Finally, the bonded devices were baked on the hotplate for 60 min at 80 °C to strengthen the bonding and retrieve the hydrophobicity of PDMS surfaces. For CTC capture experiments, the microfluidic device was connected to the solution loaded syringes using Tygon® tubing (Cole-Parmer, USA) and metallic connectors, while the injection flow rates were controlled using the syringe pumps (AL-1000, World Precision Instruments, USA).

Kajani A.A., Rafiee L., Samandari M., Mehrgardi M.A., Zarrin B, & Javanmard S.H. (2022). Facile, rapid and efficient isolation of circulating tumor cells using aptamer-targeted magnetic nanoparticles integrated with a microfluidic device. RSC Advances, 12(51), 32834-32843.

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Enzymatic p-Nitroaniline Hydrolysis

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From a 100 mM p-NA stock solution (prepared in acetonitrile, CH₃CN), a 1 mM p-NA solution in PB was freshly prepared (pH = 7.2, 1 vol% CH₃CN). This substrate solution was passed through the filter holder at 3 μL min⁻¹ for 180 min by using a syringe pump (AL1000 from World Precision Instruments). Every 3 min, 2 μL were sampled from the outflow with a Gilson Pipetman P10, and the absorption spectrum was measured with the NanoDrop One instrument (l = 0.1 cm, background: PB). Values of A₄₀₅ were taken as a measure of the formed p-nitrophenolate. The total concentration of p-nitrophenolate + p-nitrophenol in the outflow was calculated on the basis of ε₄₀₅ (p-nitrophenolate) = 10 510 M⁻¹ cm⁻¹,^{61 (link)} and [p-nitrophenolate]/[p-nitrophenol] = 1.15 at pH 7.2 using pK_a (p-nitrophenol) = 7.14.^{52 (link)} Since p-NA undergoes significant autohydrolysis, reference measurements were carried out with “empty” filters (PB only). Data for this non-enzymatic p-NA hydrolysis were subtracted from the data obtained for the filter with immobilised BCA.

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Magnetic trapping efficiency of polyelectrolyte capsules

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The magnetic trapping efficiency of 1, 2.7 and 5.5 μm PAH/PSS capsules containing different concentrations of MNPs was evaluated depending on the flow rate using a SPIM-Fluid-based custom imaging flow cytometer (Figure 2c). To perform this, the suspension of polyelectrolyte microcapsules was passed through the flow cell with the adjacent permanent magnet. Laminar suspension flow was provided by a syringe pump (AL-1000, World Precision Instruments, Sarasota, FL, USA). Objects captured by the magnetic field were counted using the computer vision method described below in the data analysis section.

Verkhovskii R., Ermakov A., Grishin O., Makarkin M.A., Kozhevnikov I., Makhortov M., Kozlova A., Salem S., Tuchin V, & Bratashov D. (2022). The Influence of Magnetic Composite Capsule Structure and Size on Their Trapping Efficiency in the Flow. Molecules, 27(18), 6073.

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Measuring Conventional Outflow Facility

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As described previously [27 (link)], the mice were anesthetized with 8% chloral hydrate (0.125 ml/20 g) and kept on a heating blanket (37 °C) during the measurement. The outflow facility was measured with a syringe-pump system. The eyes were cannulated with a 30-gauge 1/2-inch length sterile needles (Becton Dickenson), and 0.9% saline was pumped into the eye through a 100 μl Hamilton syringe, which was mounted on a computer-controlled pump (AL-1000, World Precision Instruments, Sarasota, FL). The ocular pressure transduced with a flow-through pressure sensor (Icu Medical, San Clemente, CA) was recorded in Hemo Lab software (Stauss Scientific, Iowa, IA). Three sequential pressure steps of 15, 25, and 35 mmHg were applied to the eyes, while the flow rates (μl/min) were recorded for 15 min. The averaged flow rates and the pressures at each step were used to generate a flow rate-pressure plot. The line fitting to a linear regression was added in the data set, the slope of which was considered a conventional outflow facility (μl/min/mmHg).

Fang J., Hou F., Wu S., Liu Y., Wang L., Zhang J., Wang N., Wang K, & Zhu W. (2021). Piezo2 downregulation via the Cre-lox system affects aqueous humor dynamics in mice. Molecular Vision, 27, 354-364.

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