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Biomedical subjects

Adam Heller

Publications and source records attributed to Adam Heller.

15 recordsLinked to original sources
PubMed2025

Evolution of the Artificial Pancreas: Components and Integration-CGMs, Insulin, and AP Systems.

The landmark Diabetes Control and Complications Trial (DCCT) showed that glucose control is critical to reducing the risk of diabetes-related complications. This chapter outlines a series of innovations and investigations that followed the DCCT, aimed at minimizing the risk of hypoglycemia while further improving glucose control. The chapter presents an example of innovations in wired enzyme technology that facilitated the movement from capillary glucose monitoring to continuous glucose monitoring (CGM) and ultimately, the first-factory calibrated CGM system. The next glycemic management innovation was to connect CGM data to an insulin pump containing an algorithm able to adjust insulin delivery based on the changing glucose levels and trends. The key features of automated insulin delivery (AID) systems, currently approved in the United States, are presented. The AID summary table includes type of pump, type and function of the insulin delivery algorithm, the data management system, and the indications for use. The next section explores the innovation of alternative routes of insulin delivery to move toward the goal of a fully automated insulin delivery system. The main trials in developing and implementing an implantable intraperitoneal programmable system are summarized. The last section explores if sensor input in addition to glucose levels such as continuous sensing of ketone, lactate, or insulin levels may provide valuable feedback to move us closer to a fully autonomous AID system. Much of this diabetes innovation and investigation work has been supported by the National Institute of Diabetes and Digestive and Kidney Diseases over that last 75 years.

Humans↗
PubMed2003

Enzyme-amplified amperometric detection of 3000 copies of DNA in a 10-microL droplet at 0.5 fM concentration.

We reported earlier the detection of a 38-base DNA strand at 20 pM concentration by an enzyme-amplified sandwich-type amperometric assay. The assay utilized a carbon electrode on which a redox polymer, comprising a DNA capture sequence, was electrodeposited. When present in the tested solution, part of the probed sequence hybridized with the capture probe. Hybridization of its remaining part with a horseradish peroxidase (HRP)-labeled sequence resulted in the flow of an H2O2 electroreduction current, the redox polymer wired HRP forming an electrocatalyst. Here we report a > 10(4)-fold improvement in the detection limit of the assay. DNA was detected at 0.5 fM concentration when the earlier used 3.6-mm-diameter carbon electrode was replaced by a 10-microm-diameter microelectrode. The radial diffusion of electrons through the film on the microelectrode allowed the electrodeposition of a thicker film of the redox polymer, an increase in the loading of the capture sequence, and increased the collection efficiency of the electron vacancies originating in the electroreduced H2O2. When the volume probed by the microelectrode was 10 microL, as few as 3000 copies of DNA were detected.

DNA↗
PubMed2003

Characteristics of a miniature compartment-less glucose-O2 biofuel cell and its operation in a living plant.

We report the temperature, pH, glucose concentration, NaCl concentration, and operating atmosphere dependence of the power output of a compartment-less miniature glucose-O(2) biofuel cell, comprised only of two bioelectrocatalyst-coated carbon fibers, each of 7 micro m diameter and 2 cm length (Mano, N.; Mao, F.; Heller, A. J. Am. Chem. Soc. 2002, 124, 12962). The bioelectrocatalyst of the anode consists of glucose oxidase from Aspergillus niger electrically "wired" by polymer I, having a redox potential of -0.19 V vs Ag/AgCl. That of the cathode consists of bilirubin oxidase from Trachyderma tsunodae "wired" by polymer II having a redox potential of +0.36 V vs Ag/AgCl (Mano, N.; Kim, H.-H.; Zhang, Y.; Heller, A. J. Am. Chem. Soc. 2002, 124, 6480. Mano, N.; Kim, H.-H.; Heller, A. J. Phys. Chem. B 2002, 106, 8842). Implantation of the fibers in the grape leads to an operating biofuel cell producing 2.4 micro W at 0.52 V.

Bioelectric Energy Sources↗
PubMed2003

Long tethers binding redox centers to polymer backbones enhance electron transport in enzyme "Wiring" hydrogels.

A redox hydrogel with an apparent electron diffusion coefficient (D(app)) of (5.8 +/- 0.5) x 10(-)(6) cm(2) s(-)(1) is described. The order of magnitude increase in D(app) relative to previously studied redox hydrogels results from the tethering of redox centers to the backbone of the cross-linked redox polymer backbone through 13 atom spacer arms. The long and flexible tethers allow the redox centers to sweep electrons from large-volume elements and to collect electrons of glucose oxidase efficiently. The spacer arms make the collection of electrons from glucose oxidase so efficient that glucose is electrooxidized already at -0.36 V versus Ag/AgCl, the reversible potential of the redox potential of the FAD/FADH(2) centers of the enzyme at pH 7.2. The limiting current density of 1.15 mA cm(-)(2) is reached at a potential as low as -0.1 V versus Ag/AgCl. The novel redox center of the polymer is a tris-dialkylated N,N'-biimidazole Os(2+/3+) complex. Its redox potential, -0.195 V versus Ag/AgCl, is 0.8 V reducing relative to that of Os(bpy)(2+/3+), its 2,2'-bipyridine analogue.

2,2'-Dipyridyl↗
PubMed2002

A miniature biofuel cell operating in a physiological buffer.

A glucose-O2 biofuel cell, consisting only of two electrocatalyst coated 7-mum diameter, 2-cm long carbon fibers is reported. The cell operated continuously at 0.52 V at 37 degrees C in a physiological buffer solution for a week, producing 1.9 muW during the first and 1.0 muW during the last day, generating in the period 0.9 J of electrical energy while passing a charge of 1.7 C. If a similar dimension zinc fiber were utilized in a battery at 100% current efficiency, only 0.016 C would have been generated.

Bioelectric Energy Sources↗
PubMed2002

Simple enzyme-amplified amperometric detection of a 38-base oligonucleotide at 20 pmol L(-1) concentration in a 30- microL droplet.

A 38-base DNA sequence has been detected at 20 pmol L(-1) concentration in 15-35- microL droplets by means of an electrochemical enzyme-amplified sandwich-type assay on a mass-manufacturable screen-printed carbon electrode. Formation of the sandwich brought the horseradish peroxidase-label of the detection sequence into electrical contact with a pre-electrodeposited redox polymer, making the sandwich an electrocatalyst for the reduction of hydrogen peroxide to water at +0.2 V (Ag/AgCl). Sensitivity twenty times better than that of a related system resulted from: 1. fivefold reduction of the noise by substituting the formerly used poly( N-vinyl imidazole)-co-acrylamide comprising redox co-polymer with poly(4-vinyl pyridine)-co-acrylamide comprising redox polymer, enabling use of the electrodes at a more oxidizing potential at which noise (the rate of non-enzyme catalyzed electroreduction currents of dissolved oxygen and hydrogen peroxide) was lower; 2. doubling of the catalytic electroreduction current upon electrodeposition of a second layer of the redox polymer on the capture sequence-containing film; and 3. doubling of the current by increasing the coverage by the capture sequence.

Base Sequence↗
PubMed2002

Screen printing of nucleic acid detecting carbon electrodes.

A large fraction of the presently mass-manufactured (> 10(8) units/year) electrochemical biosensors, used mostly by diabetic people to monitor their blood glucose levels, have screen-printed carbon working electrodes. An earlier study (Campbell, C. N., et al. Anal. Chem. 2002, 74, 158-162) showed that nucleic acids can be assayed at 1 nM concentrations by a sandwich-type amperometric method. The assay was performed with vitreous carbon working electrodes on which an electron-conducting polycationic redox polymer and avidin were coelectrodeposited. Because the rate of the electrodeposition increases with the surface density of the polycationic redox polymer, its practicality depends on pretreatment of the surface, which adds anionic functions. (Gao, Z., et al. Angew. Chem. Int. Ed. 2002, 41, 810-813). Here it is shown that the required conducting redox polymer films can be electrodeposited on potentially mass manufacturable electrodes made by screen-printing hydrophilic carbon inks on polyester sheets. The modified electrodes are made in two steps. First a polycationic electron-conducting redox polymer is cross-linked and electrodeposited by applying a negative potential. Next, an amine-terminated 20-base single-stranded oligonucleotide is electrodeposited by ligand-exchange. Both steps involve exchange of a labile inner sphere chloride ligand of the polymer-bound osmium-complex: Cross-linking and electrodeposition of the redox polymer result when inner-sphere chloride anions of the osmium complexes are exchanged by imidazole functions of neighboring chains. Incorporation of the oligonucleotide in the redox polymer results in the formation of a coordinative bond between the terminal amine (attached through a spacer to the oligonucleotide) and the osmium complex. In testing for the presence of a 38-base oligonucleotide, the analyte, in a 15- or 25-microL droplet of hybridization solution, is hybridized with and captured by the 20-base electrode-bound sequence; then it is hybridized with an 18-base horseradish peroxidase labeled sequence. When the HRP label electrically contacts the redox polymer, the film becomes an electrocatalyst for the reduction of H2O2 to water at 0.10 V (Ag/AgCl). Flow of the H2O2-reduction current indicates the presence of the assayed sequence.

Biosensing Techniques↗
PubMed2002

Scanning electrochemical microscopy. 44. Imaging of horseradish peroxidase immobilized on insulating substrates.

Scanning electrochemical microscopy (SECM) was used to study horseradish peroxidase (HRP) immobilized with copolymer on insulating substrates (glass slide or polycarbonate membrane filter). Two methods were used to immobilize HRP: In the first, HRP was coimmobilized by cross-linking on a glass slide with a copolymer swelled in water to form a hydrogel; in the second, the same copolymer and avidin were coimmobilized on the glass slide and biotin-labeled HRP was conjugated to the avidin of the film. SECM was then used to detect the presence of the bound enzyme by observing the feedback current in a solution of benzoquinone and hydrogen peroxide, when hydroquinone was generated at the tip. A detection limit less than 7 x 10(5) HRP molecules within a approximately 7-microm-diameter area was demonstrated.

Biosensing Techniques↗
PubMed2002

An oxygen cathode operating in a physiological solution.

We report the electroreduction of O(2) to water under physiological conditions (pH 7.4, 0.15 M NaCl, 37.5 degrees C) at a current density of 5 mA cm(-2) and at a potential only 0.18 V reducing versus that of the reversible O(2)/H(2)O electrode at pH 7.4. The immobilized electrocatalyst enabling the reduction is the electrostatic adduct of bilirubin oxidase from Myrothecium verrucaria, a polyanion at pH >4.1, and the polycationic redox copolymer of polyacrylamide and poly (N-vinylimidazole) complexed with [Os (4,4'-dichloro-2,2'-bipyridine)(2)Cl](+/2+), cross-linked on carbon cloth. The current density of the rotating electrodes was O(2) transport limited up to 8.8 mA cm(-2); their kinetic limit was reached at 9.1 mA cm(-2). The operational life of the electrodes depended on their angular velocity, which defined not only the current density but also the mechanical shear stress stripping the electrocatalyst. When the electrodes were rotated at 300 rpm and were poised at -256 mV versus the potential of the reversible O(2)/H(2)O electrode, their 2.4 mA cm(-2) initial current density decreased to 1.3 mA cm(-2) after 6 days of continuous operation at 37.5 degrees C.

Animals↗
PubMed2002

Enzyme-amplified amperometric sandwich test for RNA and DNA.

A one-step enzyme-amplified amperometric sandwich hybridization test for RNA and DNA is described. The test utilizes a carbon electrode, modified with a film of co-electrodeposited avidin and redox polymer; the redox polymer electrically "wiring" horseradish peroxidase (HRP) reaction centers upon contact. The film is made specific for the particular RNA or DNA sequence tested by conjugating its avidin with a biotinylated oligonucleotide, complementary to the assayed sequence. This oligonucleotide-modified redox polymer film, prepared prior to the test, forms the base of the sandwich. The center layer of the sandwich, added in the test, is the analyte RNA or DNA; its top is a second complemetary oligonucleotide, which is HRP-labeled, and is cohybridized in the test. The test consists of mixing the analyte DNA or RNA solution, the HRP-labeled oligonucleotide solution, and a hydrogen peroxide solution, immersing the base-layer carrying electrode applying a potential of 0 V versus Ag/AgCl, and measuring the H2O2 electroreduction current. Completion of the sandwich brings the HRP label into electrical contact with the redox polymer, converting the nonelectrocatalytic base layer into an electrocatalyst for the electroreduction of H2O2 to water. Flow of H2O2 electroreduction current when the electrode is poised near Ag/AgCl potential indicates the presence of the analyte RNA or DNA. The current density for the maximally sandwich-covered electrode was 250 microA cm(-2), exceeding more than a 100-fold the current density flowing upon nonspecific binding of the HRP-labeled oligonucleotide. High concentrations of irrelevant DNA and diluted serum did not interfere with the assay. When the electrodes were rotated in order to make the solution-phase mass transport rapid, the test was completed in approximately 30 min. The test was applied in probing for the presence of a 60-base E. coli mRNA sequence.

Animals↗
PubMed2002

Electroreduction of O(2) to water at 0.6 V (SHE) at pH 7 on the "wired" Pleurotus ostreatus laccase cathode.

O(2) was electroreduced to water at 0.6 V (SHE) near neutral pH on the "wired" Pleurotus ostreatus laccase cathode. We previously reported high-current density (5 mA cm(-2)), four-electron electroreduction of O(2) to water on a "wired" Coriolus hirsutus laccase electrode at +0.7 V (SHE) in pH 5 in citrate buffer. Since the enzyme was inhibited by chloride and because its activity declined steeply when the pH was raised to neutral, the rate of O(2) electroreduction in a physiological buffer solution was only approximately 1% of that at pH 5 in absence of chloride. Here we show that substitution of the C. hirsutus laccase by laccase from P. ostreatus allows the upward extension of the pH range of O(2) electroreduction. The current density of the electrode made with laccase from P. ostreatus in pH 7 citrate buffer was approximately 100 microA cm(-2) and at pH 7 and in phosphate buffered NaCl (PBS, 20 mM phosphate, 0.1 M NaCl) it still retained 6% of its maximal (1 mA cm(-2)) current density at pH 5 in citrate buffer. The electrocatalyst consisted of the crosslinked P. ostreatus laccase and the electron conducting redox polymer PVI-Os(dmebpy)(tpy)(2+/3+) [PVI=poly(N-vinyl imidazole) with about 1/5th of the rings complexed with (Os-dmebpy-tpy)(2+/3+); dmebpy=4,4'-dimethyl-2,2'-bipyridine; tpy=2,2',6',2"-terpyridine].

Bioelectric Energy Sources↗
PubMed2002

Defining the period of recovery of the glucose concentration after its local perturbation by the implantation of a miniature sensor.

At the wound caused by implanting a subcutaneous glucose sensor, the concentration of glucose differs transiently from that in the subcutaneous fluid near non-wounded skin. The period of recovery differs for different wounds and is difficult to predict. A diabetic patient implanting a subcutaneous sensor needs to know whether the transient difference subsided sufficiently for the sensor readings and the sensor's in vivo calibration to be valid. The miniature amperometric glucose sensor has a compound membrane including a layer of glucose oxidase the reaction centers of which are electrically connected to the electrode through a redox polymer; layers excluding interferents and poisons of the electrocatalytic oxidation of glucose; and a layer reducing fouling by components of the biological fluids. We show that the sensor maintains its in vitro sensitivity after its implantation for four hours in the jugular vein and in the peritoneal fluid of the rat. For a diabetic patient who implants the sensor the four-hour period is long enough for the insertion-trauma-caused local perturbation of the glucose concentration to subside and to safely rely on the readings of the implanted sensor.

Animals↗