# US 2013/0153443 A1 · Device for measuring proteins using biosensor

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- Number: US 2013/0153443 A1
- Document ID: US20130153443A1
- Status: Published application
- Kind: A1
- Application number: 13/732,733
- Filed: 2013-01-02
- Published: 2013-06-20
- Earliest claimed: 2008-07-15
- Assignees: I-Sens, Inc.
- Inventors: Hakhyun Nam; Su-Moon Park; Jin-Young Park; Joo Young Cho
- Web page: https://patentgrep.com/patent/US20130153443A1

## CPC

- G01N 27/02: by investigating impedance
- G01N 27/3276: {being a hybridisation with immobilised receptors (using a FET type sensor G01N27/4145; concerning the hybridisation C12Q1/68)}
- G01N 33/5438: {Electrodes}
- G01N: INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES (measuring or testing apparatus or processes other than immunoassay, involving enzymes or microorganisms C12M, C12Q)

## Abstract

A sensor for measuring a concentration of a specific protein using a biosensor with a measurement speed improved from a conventional impedance measurement. The sensor is capable of efficiently and accurately measuring impedance generated by a selective binding to the protein by Fourier-transforming an electric current signal obtained by applying a potential signal of a delta function waveform. The device for measuring a protein using a biosensor is capable of measuring concentration of the protein with accuracy, measurement time is shortened and the concentration of protein can be accurately measured by removing the influence of dispersion.

## Claims

### Claim at position 1

1-13. (canceled)

### Claim 14

A method of measuring a concentration of a specific protein using a biosensor comprising:
feeding a sample comprising the specific protein into a biosensor;
wherein the biosensor comprises a sample inlet through which the sample is drawn in, a working electrode on which a receptor layer is coated for selective binding to the specific protein in the drawn sample, and a measuring unit comprising a reference electrode to form a potential difference with the working electrode,
applying a potential signal in a form of delta function waveform to the working electrode and the reference electrode; and
measuring an impedance of the working electrode by Fourier-transforming an electric current obtained in response to the delta function waveform.

### Claim 15 (depends on 14)

The method of claim 14, wherein the specific protein is a glycated protein.

### Claim 16 (depends on 14)

The method of claim 14, wherein,
the specific protein is a glycated hemoglobin;
the sample is a measuring solution comprising a hemolysis reagent, a buffer solution, an ion of Fe3+ and a sample of blood; and
the working electrode is coated with a self-assembled monolayer (SAM) which have boronic acid derivative as an end group.

### Claim 17 (depends on 14)

The method of claim 14, wherein the measuring unit further comprises an auxiliary electrode to measure impedance of the working electrode, and the potential signal is applied between the working electrode and the auxiliary electrode.

### Claim 18 (depends on 14)

The method of claim 14, wherein the concentration of the specific protein is measured by measuring impedance generated on the working electrode by selective binding to the receptor layer.

### Claim 19 (depends on 14)

The method of claim 14, wherein the potential signal is applied as a step potential signal by integrating the delta function waveform.

### Claim 20 (depends on 14)

The method of claim 14, wherein the biosensor further comprises an air outlet for the sample to move through the sample inlet to the measuring unit by capillary phenomenon.

### Claim 21 (depends on 16)

The method of claim 16, further comprising measuring a concentration of a hemoglobin contained in the sample by an oxidation-reduction reaction of the hemoglobin using other electrochemical biosensor which is connected to the sample inlet through a micro channel.

### Claim 22 (depends on 1)

The method of claim 1, wherein the working electrode is made from gold or white gold.

### Claim 23 (depends on 22)

The method of claim 22, wherein the receptor layer is formed as a self-assembled monolayer having boronic acid derivative as an end group, and the boronic acid derivative is partially transformed into a thiol group to easily combine with a gold electrode.

### Claim 24 (depends on 14)

The method of claim 14, wherein the impedance occurs when electron transfer of an oxidation-reduction pair is inhibited by the specific protein selectively binding to the receptor layer on the working electrode.

### Claim 25 (depends on 24)

The method of claim 24, wherein the oxidation-reduction pair is selected from a group consisting of ferrocene, ferrocene derivatives, quinones, quinines derivatives, organic conducting salt, or viologen, hexaammineruthenium (III) chloride, dimethylferrocene (DMF), ferricinium, ferocene monocarboxylic acid (FCOOH), 7,7,8,8-tetracyanoquino-dimethane (TCNQ), tetrathia fulvalene (TTF), nickelocene (Nc), N-methyl acidinium (NMA+), tetrathiatetracene (TTT), N-methylphenazinium (NMP+), hydroquinone, 3-dimethylaminobenzoic acid (MBTHDMAB), 3-methyl-2-benzothiozolinone hydrazone, 2-methoxy-4-allylphenol, 4-aminoantipyrin (AAP), dimethylaniline, 4-aminoantipyrene, 4-methoxynaphthol, 3,3′,5,5′-tetramethyl benzidine (TMB), 2,2-azino-di-[3-ethyl-benzthiazoline sulfonate], o-dianisidine, o-toluidine, 2,4-dichlorophenol, 4-amino phenazone, benzidine and prussian blue.