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ref: -0 tags: photoacoustic tomography mouse imaging q-switched laser date: 05-11-2017 05:23 gmt revision:1 [0] [head]

Single-impulse panoramic photoacoustic computed tomography of small-animal whole-body dynamics at high spatiotemporal resolution

  • Used Q-switched Nd:YAG and Ti:Sapphire lasers to illuminate mice axially (from the top, through a diffuser and conical lens), exciting the photoacuostic effect, from which they were able to image at 125um resolution a full slice of the mouse.
    • I'm surprised at their mode of illumination -- how do they eliminate the out-of-plane photoacoustic effect?
  • Images look low contrast, but structures, e.g. cortical vasculature, are visible.
  • Can image at the rep rate of the laser (50 Hz), and thereby record cardiac and pulmonary rhythms.
  • Suggest that the photoacoustic effect can be used to image brain activity, but spatial and temporal resolution are limited.

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ref: -0 tags: photoacoustic tomography mouse imaging q-switched laser date: 05-11-2017 05:21 gmt revision:0 [head]

Single-impulse panoramic photoacoustic computed tomography of small-animal whole-body dynamics at high spatiotemporal resolution

  • Used Q-switched Nd:YAG and Ti:Sapphire lasers to illuminate mice axially, exciting the photoacuostic effect, from which they were able to image at 125um resolution a full slice of the mouse.
  • Images look low contrast, but structures, e.g. cortical vasculature, are visible.
  • Can image at the rep rate of the laser (50 Hz), and thereby record cardiac and pulmonary rhythms.
  • Suggest that the photoacoustic effect can be used to image brain activity, but spatial and temporal resolution are limited.

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ref: -0 tags: electrode area review impedance date: 04-28-2017 17:55 gmt revision:9 [8] [7] [6] [5] [4] [3] [head]

Quick review of electrode area / impedance within m8ta:

  • {895} 500um^2
  • {311} 490um^2 nominal; 900k
  • {1040} 108um^2, plated from 5M to 1M.
  • Neuronexus: 177, 413um, 700um, and 1250um.
    • Suggest 177um for SUA, 413um for MUA.
    • Community consensus seems to be that these electrodes don't last as long, though.
    • Electroplating 177um^2 sites with PEDOT:PSS reduces impedance to 23k {1388}
  • {823} 122um^2 nominal
  • {736} 500um^2
  • {1027} (Utah) 1600um^2
    • Impedance: ~ 220K +-91K (in vivo -- large variance)
    • Blackrock site lists impedance @ 400k
  • SIrOF Utah array -- 3100um^2 (3.1e-5cm^2) -- large!
    • Impedance ~50K according to [www.blackrockmicro.com/userfiles/file/Microelectrode%20Arrays.pdf Blackrock product brochure].
  • PMID-20124668 (Utah again) 2000um^2, 125k Pt, 6k SIROF.
  • Neuropixel: 144um^2 acid-etched TiN
  • Carbon fiber: ~38 um^2, PEDOT:PSS or PEDOT:pTS started ~ 4M, plated down to ~ 130k initial, went up to 2M pSS, 840k pTS.

{1356}
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ref: -2016 tags: Kozai carbon fiber microelectrodes JNE PEDOT PSS pTS date: 04-27-2017 01:42 gmt revision:6 [5] [4] [3] [2] [1] [0] [head]

PMID-27705958 Chronic in vivo stability assessment of carbon fiber microelectrode arrays.

  • showed excellent recording characteristics and nearly zero glial scarring.
  • 6.4um carbon fiber + 800nm parylene-C = 8.4um.
    • Cytec Thoronel T-650 CF, Youngs modulus = 255 GPa, tensile strength = 4.28 GPa, PAN-based.
  • Everything protected with our wonderful phenol epoxy 353NDT, heat-cure.
  • Used two coating solutions:
    • Solution of 0.01 M 3,4-ethylenedioxythiophene (483028, Sigma-Aldrich, St. Louis, MO): 0.1 M sodium p-toluenesulfonate (152536, Sigma-Aldrich, St. Louis, MO).
      • pTS is not that dissimilar from it's alkyl cousin, SPS, {1353}. Likely a soapy chemical due to the opposed methyl and sulfonic acid group; benzine will take up less room in the polymer c.f. SDS & may lower the oxidation potential of EDOT.
      • Tosylates have been explored as a EDOT counterion : PMID-22383043 Characterization of poly(3,4-ethylenedioxythiophene):tosylate conductive polymer microelectrodes for transmitter detection. and PEDOT-TMA
    • Solution was composed of 0.01 M 3,4-ethylene-dioxythiophene (483028, Sigma-Aldrich, St. Louis, MO):0.1 M polystyrene sulfonate (m.w. 70.000, 222271000, Acros, NJ).
    • For each solution the electrodeposition was carried out by applying 100 pA/channel for 600 s to form a layer of poly(3,4-ethylenedioxythiophene):sodium p-toluenesulfonate (PEDOT:pTS) or poly(3,4-ethylenedioxythiophene):polystyrene sulfonate (PEDOT:PSS).
      • Weird, would use voltage control here..
  • According to works by Green et al [45] and Hukins et al [46], equation (1) can be used to determine the aging time that
the fibers have undergone: t 37=t TQ10 T37)/10 where t 37 is the simulated aging time at 37 °C, t T is the amount of real time that the samples have been kept at the elevated temperature, T , and Q10 is an aging factor that is equal to 2, according to ASTM guidelines for polymer aging [47].
  • Show > 2MOhm impedance of the small-area electrodes. At the aging endpoint, PEDOT:pTS had about half the impedance of PEDOT:PSS.
    • 4M PSS, 7M pTS, both plated down to ~ 130k initial, went up to 2M pSS, 840k pTS.
  • Recording capability quite stellar
  • Likewise for the glial response.

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ref: -0 tags: PEDOT PSS electroplate eletrodeposition neural recording michigan probe stimulation CSC date: 04-27-2017 01:36 gmt revision:1 [0] [head]

PMID-19543541 Poly(3,4-ethylenedioxythiophene) as a micro-neural interface material for electrostimulation

  • 23k on a 177um^2 site.
  • demonstrated in-vitro durable stimulation.
  • Electrodeposited with 6na for 900 seconds per electrode.
    • Which is high -- c.f. 100pA for 600 seconds {1356}
  • Greater CSC and lower impedance / phase than (comparable?) Ir or IrOx plating.

{1387}
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ref: -1977 tags: polyethylene surface treatment plasma electron irradiation mechanical testing saline seawater accelerated lifetime date: 04-15-2017 06:06 gmt revision:0 [head]

Enhancement of resistance of polyethylene to seawater-promoted degradation by surface modification

  • Polyethylene, when repeatedly stressed and exposed to seawater (e.g. ships' ropes), undergoes mechanical and chemical degradation.
  • Surface treatments of the polyethlyene can improve resistance to this degradation.
  • The author studied two methods of surface treatment:
    • Plasma (glow discharge, air) followed by diacid (adipic acid) or triisocyanate (DM100, = ?) co-polymerization
    • Electron irradiation with 500 kEV electrons.
  • Also mention CASING (crosslinking by activated species of inert gasses) as a popular method of surface treatment.
    • Diffuse-in crosslinkers is a third, popular these days ...
    • Others diffuse in at temperature e.g. a fatty acid - derived molecule, which is then bonded to e.g. heparin to reduce the thrombogenicity of a plastic.
  • Measured surface modifications via ATR IR (attenuated total reflectance, IR) and ESCA (aka XPS)
    • Expected results, carbonyl following the air glow discharge ...
  • Results:
    • Triisocyanate, ~ 6x improvement
    • diacid, ~ 50 x improvement.
    • electron irradiation, no apparent degradation!
      • Author's opinion that this is due to carbon-carbon crosslink leading to mechanical toughening (hmm, evidence?)
  • Quote: since the PE formulation studied here was low-weight, it was expected to lose crystallinity upon cyclic flexing; high density PE's have in fact been observed to become more crystalline with working.
    • Very interesting, kinda like copper. This could definitely be put to good use.
  • Low density polyethylene has greater chain branching and entanglement than high-density resins; when stressed the crystallites are diminished in total bulk, degrading tensile properties ... for high-density resins, mechanical working loosens up the structure enough to allow new crystallization to exceed stress-induced shrinkage of crystallites; hence, the crystallinity increases.

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ref: -0 tags: tungsten eletropolishing hydroxide cleaning bath tartarate date: 03-28-2017 16:34 gmt revision:0 [head]

Method of electropolishing tungsten wire US 3287238 A

  • The bath is formed of 15% by weight sodium hydroxide, 30% by weight sodium potassium tartrate, and 55% by weight distilled water, with the bath temperature being between 70 and 100 F.
    • If the concentration of either the hydroxide or the tartrate is below the indicated minimum, the wire is electrocleaned rather than electropolished, and a matte finish is obtained rather than a specular surface.
    • If the concentration of either the hydroxide or the tartrate is greater than the indicated maximum, the electropolishing process is quite slow.
  • The voltage which is applied between the two electrodes 18 and 20 is from 16 to 18.5 volts, the current through the bath is 20 to 24 amperes, and the current density is 3,000 to 4,000 amperes per square foot of surface of wire in the bath.

{1250}
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ref: -0 tags: polyimide electrodes thermosonic bonding Stieglitz adhesion delamination date: 03-06-2017 21:58 gmt revision:7 [6] [5] [4] [3] [2] [1] [head]

IEEE-6347149 (pdf) Improved polyimide thin-film electrodes for neural implants 2012

  • Tested adhesion to Pt / SiC using accelerated aging in saline solution.
  • Targeted at retinal prostheses.
  • Layer stack:
    • 50nm SiC deposited through PECVD @ 100C using SPS, with low frequency RF modulation.
    • 100nm Pt
    • 100nm Au
    • 100nm Pt
      • These layers will alloy during cure, and hence reduce stress.
    • 30nm SiC
    • 10nm DLC (not needed, imho; PI sticks exceptionally well to clean SiC)
  • Recent studies have concluded that adhesion to PI is through carbon bindings and not through oxide formation.
    • Adhesion of polyimide to amorphous diamond-like carbon and SiC deteriorates at a minimal rate.
  • Delamination is caused by residual stress, which is not only inevetable but a major driving force for cracking in thin films.
    • Different CTE in layer stack -> different contraction when cooling from process temperature.
  • Platinum, which evaporates at 1770C, and is deposited ~100C (photoresists only withstand ~115C) results in a high-stress interface.
    • Pt - Carbon bonds only occur above 1000C
  • After 9 and 13 days of incubation the probes with 400 nm and 300nm of SiC, respectively, which were not tempered, showed complete delamination of the Pt from the SiC.
    • 60C, 0.9 M NaCl, 1 year.
    • The SiC remained attached to the PI.
      • Tempering: repeated treatment at 450C for 15 min in a N2 atmosphere.
    • All other probes remained stable.
  • Notably, used thermosonic bonding to the PI films, using sputtered (seed layer) then 12um electroplated Au.
  • Also: fully cured the base layer PI film.
  • Used oxygen plasma de-scum after patterning with resists to get better SiC adhesion to PI.
    • And better inter-layer adhesion (fully cured the first polyimide layer @ 450C).
  • Conclusion: "The fact that none of the tempered samples delaminated even after ~5 years of lifetime (extrapolated for 37 C) shows a tremendous increase in adhesion.

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ref: -0 tags: NET probes SU-8 microfabrication sewing machine carbon fiber electrode insertion mice histology 2p date: 03-01-2017 23:20 gmt revision:0 [head]

Ultraflexible nanoelectronic probes form reliable, glial scar–free neural integration

  • SU-8 asymptotic H2O absorption is 3.3% in PBS -- quite a bit higher than I expected, and higher than PI.
  • Faced yield problems with contact litho at 2-3um trace/space.
  • Good recordings out to 4 months!
  • 3 minutes / probe insertion.
  • Fab:
    • Ni release layer, Su-8 2000.5. "excellent tensile strength" --
      • Tensile strength 60 MPa
      • Youngs modulus 2.0 GPa
      • Elongation at break 6.5%
      • Water absorption, per spec sheet, 0.65% (but not PBS)
    • 500nm dielectric; < 1% crosstalk; see figure S12.
    • Pt or Au rec sites, 10um x 20um or 30 x 30um.
    • FFC connector, with Si substrate remaining.
  • Used transgenic mice, YFP expressed in neurons.
  • CA glue used before metabond, followed by Kwik-sil silicone.
  • Neuron yield not so great -- they need to plate the electrodes down to acceptable impedance. (figure S5)
    • Measured impedance ~ 1M at 1khz.
  • Unclear if 50um x 1um is really that much worse than 10um x 1.5um.
  • Histology looks realyl great, (figure S10).
  • Manuscript did not mention (though the did at the poster) problems with electrode pull-out; they deal with it in the same way, application of ACSF.

{1176}
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ref: Gilgunn-2012 tags: kozai neural recording electrodes compliant parylene flexible dissolve date: 02-24-2017 19:14 gmt revision:5 [4] [3] [2] [1] [0] [head]

IEEE-6170092 (pdf) An ultra-compliant, scalable neural probe with molded biodissolvable delivery vehicle

    • Optical coherence tomography is cool.
  • Large footprint - 150 or 300um, 135um thick (13500 or 40500 um^2; c.f. tungsten needle 1963 (50um) or 490 (25um) um^2.)
  • Delivery vehicle is fabricated from biodissolvable carboxy-methylcellulose (CMC).
    • Device dissolves within three minutes of implantation.
    • Yet stiff enough to penetrate the dura of rats (with what degree of dimpling?)
    • Lithographic patterning process pretty clever, actually.
    • Parylene-X is ~ 1.1 um thick.
    • 500nm Pt is patterned via ion milling with a photoresist mask.
    • Use thin 20nm Cr etch mask for both DRIE (STS ICP) and parylene etch.
  • Probes are tiny -- 10um wide, 2.7um thick, coated in parylene-X.
  • CMC polymer tends to bend and warp due to stress -- must be clamped in a special jig.
  • No histology. Follow-up?

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ref: Seymour-2007.09 tags: neural probe design recording Kipke Seymour parelene MEA histology PEDOT date: 02-23-2017 23:52 gmt revision:13 [12] [11] [10] [9] [8] [7] [head]

PMID-17517431[0] Neural probe design for reduced tissue encapsulation in CNS.

  • See conference proceedings too: PMID-17947102[1] Fabrication of polymer neural probes with sub-cellular features for reduced tissue encapsulation.
    • -- useful information.
  • They use SU8 - photoresist! - as a structural material. See also this.
    • They use silicon as a substrate for the fabrication, but ultimately remove it. Electrodes could be made of titanium, modulo low conductivity.
  • Did not / could not record from these devices. Only immunochemistry.
  • Polymer fibers smaller than 7um are basically invisible to the immune system. See [2]
  • Their peripheral recording site is 4 x 5um - but still not invisible to microglia. Perhaps this is because of residual insertion trauma, or movement trauma? They implanted the device flush with the cortical surface, so there should have been little cranial tethering.
  • Checked the animals 4 weeks after implantation.
  • Peripheral electrode site was better than shank location, but still not perfect. Well, any improvement is a good one...
  • No statistical difference between 4x5um lattice probes, 10x4um probes, 30x4um, and solid (100um) knife edge.
    • Think that this may be because of electrode micromotion -- the lateral edge sites are still relatively well connected to the thick, rigid shank.
  • Observed two classes of immune reactivity --
    • GFAP reactive hypertrophied astrocytes.
    • devoid of GFAP, neurofilament, and NEuN, but always OX-42 and often firbronectin and laminin positive as well.
    • Think that the second may be from meningeal cells pulled in with the stab wound.
  • Sensitivity is expected to increase with decreased surface area (but similar low impedance -- platinum black or oxidized iridium or PEDOT {1112} ).
  • Thoughts: it may be possible to put 'barbs' to relieve mechanical stress slightly after the probe location, preferably spikes that expand after implantation.
  • His thesis {1110}

____References____

[0] Seymour JP, Kipke DR, Neural probe design for reduced tissue encapsulation in CNS.Biomaterials 28:25, 3594-607 (2007 Sep)
[1] Seymour JP, Kipke DR, Fabrication of polymer neural probes with sub-cellular features for reduced tissue encapsulation.Conf Proc IEEE Eng Med Biol Soc 1no Issue 4606-9 (2006)
[2] Sanders JE, Stiles CE, Hayes CL, Tissue response to single-polymer fibers of varying diameters: evaluation of fibrous encapsulation and macrophage density.J Biomed Mater Res 52:1, 231-7 (2000 Oct)

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ref: Schmidt-1993.11 tags: Normann utah array histology silicon electrode array cats date: 02-23-2017 22:03 gmt revision:4 [3] [2] [1] [0] [head]

PMID-8263001[0] Biocompatibility of silicon-based electrode arrays implanted in feline cortical tissue.

  • Tried two different times:
    • one day before euthanasia
    • 6 month implant.
  • Tried three different implants:
    • Uncoated silicon,
    • polymide coating
    • polymide coating with SiO2 adhesion layer / primer.
  • The last was the worst in terms of histopathological response.
  • Chronic implants showed relatively restrained immune response,
    • Gliosis was found around all tracks, 20-40um.
  • Encapsulation was less than 9um.
  • Edema and hemorrhage was minor but present on a subset of all implants.
  • Acute (24h) hemorrhage was more severe -- ~ 60%; edema ~ 20%.
  • Chronic histology revealed considerable macrophages w/ hemosiderin (a complex including ferritin)
  • See also [1]

____References____

[0] Schmidt S, Horch K, Normann R, Biocompatibility of silicon-based electrode arrays implanted in feline cortical tissue.J Biomed Mater Res 27:11, 1393-9 (1993 Nov)
[1] Jones KE, Campbell PK, Normann RA, A glass/silicon composite intracortical electrode array.Ann Biomed Eng 20:4, 423-37 (1992)

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ref: -0 tags: carbon nanotube densification conductivity strength date: 02-23-2017 02:52 gmt revision:2 [1] [0] [head]

Super-strong and highly conductive carbon nanotube ribbons from post-treatment methods

  • Conductivity of 1.2e6 S/m, about that of stainless steel.
    • 500 x 500nm wire, length 1cm will have a resistance of 40k.
  • Aerogel method: methane + ferrocene + thiophene + hydrogen.
    • Resulting in ~ 18% Fe, multi-walled carbon nanotubes, diameter 15nm, 15-20 walls.
  • Densified with a stainless-steel spatula on regular paper.
    • Resulting in ribbons 22um wide, 650nm thick.
  • Very high tensile strength, up to 5.2 GPa; moduls ~ 266 GPa.

High-strength carbon nanotube fibre-like ribbon with high ductility and high electrical conductivity

  • Slightly higher conductivity, 1.82 - 2.24e6 S/m.
  • Rolled until it was 500nm thick!
  • Spun from an aerogel (!!) using ethanol + ferrocent + thiophene.

{1382}
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ref: -0 tags: iridium oxide nanotube intracellular recording electroplate MEA date: 02-22-2017 22:41 gmt revision:0 [head]

PMID-24487777 Iridium oxide nanotube electrodes for sensitive and prolonged intracellular measurement of action potentials.

  • Electrodeposition of IrOx "magically" forms 500nm tubes.
  • Holes in Si3N4 / SiO2 were formed via e-beam lithography; underlying Pt wires via liftoff.
  • Showed long (minutes) intracellular access, though it tended to dip with time.

{1381}
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ref: -0 tags: glassy carbon SU-8 pyrolysis CEC microelectrode stimulation stability platinum PEDOT date: 02-17-2017 00:05 gmt revision:2 [1] [0] [head]

A novel pattern transfer technique for mounting glassy carbon microelectrodes on polymeric flexible substrates

  • Use inert-atmosphere pyrolysis @ 900 - 1000 C of 20um SU-8 (which is aromatic) on a thermal oxide wafer.
  • Followed by spin & cure of PI.
  • Demonstrate strong carbonyl bonding of the glassy carbon with mechanical and FTIR testing.
  • Use of photosensitive PI allows through-vias to connect Cr/Au conductive traces.

PMID-28084398 Highly Stable Glassy Carbon Interfaces for Long-Term Neural Stimulation and Low-Noise Recording of Brain Activity

  • Use EIS to show superior charge-injection properties + stability of glassy carbon electrodes vs. Pt electrodes.
    • GC lasted > 5e6 pulses; Pt electrodes delaminated after 1e6 pulses.
    • Hydrogen bonding (above) clearly superior than neat PI-Pt interface
  • GC electrodes were, true to their name, glassy and much smoother than the platinum electrodes.
  • Further reduced impedance with PEDOT-PSS coating.
    • PEDOT-PSS coating on glassy carbon was, in their hands, far more stable than PEDOT-PSS on platinum.
  • All devices, GC, PEDOT:PSS, and Pt, had similar biocompatibility in their assay (figure 7)

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ref: -0 tags: myoelectric EMG recording TMR prosthetics date: 02-13-2017 20:43 gmt revision:0 [head]

PMID: Man/machine interface based on the discharge timings of spinal motor neurons after targeted muscle reinnervation

  • General idea: deconvolve a grid-recorded EMG signal to infer the spinal motorneron spikes, and use this to more accurately decode user intention.
  • EMG envelope is still fairly good...

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ref: -0 tags: polypyrrole date: 02-09-2017 01:26 gmt revision:0 [head]

PMID-23307738 Bio-inspired Polymer Composite Actuator and Generator Driven by Water Gradients

  • Alas, water gradient driven, not electrically driven. Still, highly interesting ... check out the videos.

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ref: -0 tags: carbon fiber thread spinning Pasquali Kemere nanotube stimulation date: 02-09-2017 01:09 gmt revision:0 [head]

PMID-25803728 Neural stimulation and recording with bidirectional, soft carbon nanotube fiber microelectrodes.

  • Poulin et al. demonstrated that microelectrodes made solely of CNT fibers22 show remarkable electrochemical activity, sensitivity, and resistance to biofouling compared to conventional carbon fibers when used for bioanalyte detection in vitro.23-25
  • Fibers were insulated with 3 um of block copolymer polystyrene-polybutadiene (PS-b-PBD) (polybutadiene is sythetic rubber)
    • Selected for good properties of biocompatibility, flexibility, resistance to flextural fatigue.
    • Available from Sigma-Aldrich.
    • Custom continuous dip-coating process.
  • 18um diameter, 15 - 20 x lower impedance than equivalently size PtIr.
    • 2.5 - 6x lower than W.
    • In practice, 43um dia, 1450um^2, impedance of 11.2 k; 12.6um, 151k.
  • Charge storage capacity 327 mC / cm^2; PtIr = 1.2 mC/cm^2
  • Wide water window of -1.5V - 1.5V, consistent with noble electrochemical properties of C.
  • Lasts for over 97e6 pulsing cycles beyond the water window, vs 43e6 for PEDOT.
  • Tested via 6-OHDA model of PD disease vs. standard PtIr stimulating electrodes, implanted via 100um PI shuttled attached with PEG.
  • Yes, debatable...
  • Tested out to 3 weeks durability. Appear to function as well or better than metal electrodes.

PMID-23307737 Strong, light, multifunctional fibers of carbon nanotubes with ultrahigh conductivity.

  • Full process:
    1. Dissolve high-quality, 5um long CNT in chlorosulfonic acid (the only known solvent for CNTs)
    2. Filter to remove particles
    3. Extrude liquid crystal dope through a spinneret, 65 or 130um orifice
    4. Into a coagulant, acetone or water
    5. Onto a rotating drum to put tension on the thread & align the CNTs.
    6. Wash in water and dry at 115C.
  • Properties:
    • Tensile strength 1 GPa +- 0.2 GPa.
    • Tensile modulus 120 GPa +- 50, best value 200 GPa
      • Pt: 168 GPa ; Au: 79 GPa.
    • Elongation to break 1.4 %
    • Conductivity: 0.3 MS/m, Iodine doped 5 +- 0.5 MS/m (22 +- 4 microhm cm)
      • Cu: 59.6 MS/m ; Pt: 9.4 MS/m ; Au: 41 MS/m
      • Electrical conductivity drops after annealing @ 600C
      • But does not drop after kinking and repeated mechanical cycling.
  • Theoretical modulus of MWCNT ~ 350 GPa.
  • Fibers well-aligned at ~ 90% the density (measure 1.3 g/cc) of close-packed CNT.

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ref: -0 tags: nanoprobe transmembrane intracellular thiol gold AFM juxtacellular date: 02-06-2017 23:45 gmt revision:3 [2] [1] [0] [head]

PMID-20212151 Fusion of biomimetic stealth probes into lipid bilayer cores

  • Used e-beam evaporation of Cr/Au/Cr 10/10/10 or 10/5/10 onto a Si AFM tip.
    • Approx 200nm diameter; 1800 lipid interaction at the circumference.
  • Exposed the Au in the sandwich via FIB
  • Functionalized the Au with butanethiol or dodecanthiol; former is mobile on the surface, latter is polycrystaline.
    • Butanethiol showed higher adhesion to the synthetic membranes
  • Measured the penetration force & displacement through synthetic multi-layer lipid bilayers.
    • These were made via a custom protocol with 1-stearoyl-2-oleoyl-sn-glycero-3-phosphocholine (SOPC) and cholesterol

PMID-21469728 '''Molecular Structure Influences the Stability of Membrane Penetrating Biointerfaces.

  • Surprisingly, hydrophobicity is found to be a secondary factor with monolayer crystallinity the major determinate of interface strength
  • Previous studies using ellipsometry and IR spectroscopy have shown that alkanethiol self-assembled monolayers display an abrupt transition from a fluid to a crystalline phase between hexanethiol and octanethiol.
    • This suggests the weakening of the membrane stealth probe interface is due to the crystallinity of the molecular surface with fluid, disordered monolayers promoting a high strength interface regime and rigid, crystalline SAMs forming weak interfaces.