WO2003096002A1 - Instrument et procede de mesure du signal d'action d'un echantillon biologique - Google Patents
Instrument et procede de mesure du signal d'action d'un echantillon biologique Download PDFInfo
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- WO2003096002A1 WO2003096002A1 PCT/JP2003/005735 JP0305735W WO03096002A1 WO 2003096002 A1 WO2003096002 A1 WO 2003096002A1 JP 0305735 W JP0305735 W JP 0305735W WO 03096002 A1 WO03096002 A1 WO 03096002A1
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- biological sample
- measurement
- activity
- activity signal
- measuring
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/483—Physical analysis of biological material
- G01N33/487—Physical analysis of biological material of liquid biological material
- G01N33/48707—Physical analysis of biological material of liquid biological material by electrical means
- G01N33/48728—Investigating individual cells, e.g. by patch clamp, voltage clamp
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
- G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
- G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
- G01N33/54366—Apparatus specially adapted for solid-phase testing
- G01N33/54373—Apparatus specially adapted for solid-phase testing involving physiochemical end-point determination, e.g. wave-guides, FETS, gratings
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
- G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
- G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
- G01N33/54366—Apparatus specially adapted for solid-phase testing
- G01N33/54373—Apparatus specially adapted for solid-phase testing involving physiochemical end-point determination, e.g. wave-guides, FETS, gratings
- G01N33/5438—Electrodes
Definitions
- the present invention relates to an apparatus and a method for measuring an activity signal emitted from a biological sample such as a cell.
- a physicochemical signal emitted in accordance with the activity of a biological sample is taken into a measuring device and measured as an electrical signal or a digital signal such as a fluorescence intensity signal emitted by an indicator taken into the biological sample.
- a digital value representing the amount of electricity passing through the channel obtained by an electrophysiological measurement device using a microelectrode probe such as a patch clamp and a dedicated control device. It is measured by calculating the channel opening / closing time, timing, number of times, etc. from the signal.
- the patch clamp method is a method in which the transport of ions through a single channel protein molecule is electrically recorded by a microelectrode probe using a micropart (patch) of the cell membrane attached to the tip of the micropit.
- Patch clamp is one of the few cell biology techniques that can examine the function of a single protein molecule in real time (eg, molecular biology of cells, 3rd edition, Gar 1 and Publ. Ng, Inc.> New York, 1994, Japanese version, translated by Keiko Nakamura et al., Pp. 181-282, 1995, see Kyoikusha).
- the fluorescent dye method is a method for measuring the electrical activity of cells by combining a luminescence indicator or a fluorescent dye that emits light in accordance with a change in the concentration of a specific ion with an image processing method. For example, the movement of ions in cells is monitored based on fluorescence images of cells taken using a CCD camera.
- the ion channel activity of the whole cell is generally measured by the total amount of ions flowing into the cell by a fluorescence measurement method.
- the patch-clamp method requires special techniques for micropipette fabrication and manipulation, and it takes a lot of time to measure one sample. Not.
- the fluorochrome method can rapidly screen a large number of drug candidate compounds, but requires a step of staining cells, and in measurement, the background due to the effect of the dye is high and the color is decolorized with time. There is a disadvantage that the SZN ratio is poor.
- the present invention discloses an integrated composite electrode characterized by forming microelectrodes on a substrate by using photolithographic technique and capable of measuring electrical changes of cells extracellularly at multiple points, and a measurement system using the same.
- International Publication No. WO 01/25759 discloses a method in which a through-hole is provided on an insulating substrate, and a biological sample such as a cell containing an ion channel is placed in the through-hole, so that a cell or the like and the surface of the insulating substrate are disposed.
- a substrate that constitutes a giga shield and can measure a current generated when ions pass through an ion channel by using a reference electrode and a measurement electrode provided in two regions separated by the giga shield. .
- U.S. Patent No. 5,187,699 discloses a device that can monitor cell growth by culturing cells on electrodes and measuring the change in impedance.
- WO 99/66632 9 discloses a device for observing the state of activity of cells on a porous material by resistance or impedance change, and an assay method using the same.
- International Publication No. WO 99/31503 discloses a method of forming a patch clamp by trapping cells in a through-hole using a substrate having a through-hole and measuring a change in current.
- An object of the present invention is to provide an apparatus and a method for measuring an activity signal of a biological sample, which can easily, quickly and accurately detect an activity signal generated by the biological sample.
- the object of the present invention is an apparatus for measuring an activity signal of a biological sample, comprising: a measurement chamber containing a liquid to be measured containing a biological sample; a porous insulating substrate provided with a measurement electrode on at least one surface; A transport device that transports the liquid to be measured in the measurement chamber and passes the porous insulating substrate from the measurement electrode side, and operates the transport device to measure the biological sample contained in the liquid to be measured.
- a biological sample activity signal measuring device capable of measuring an activity signal of a biological sample via the measurement electrode by capturing at the electrode.
- the object of the present invention is a method for measuring an activity signal of a biological sample, comprising: a step of injecting a liquid to be measured containing the biological sample into a measuring chamber; and a step of transporting the liquid to be measured from the measuring chamber.
- a living body comprising: a step of capturing a biological sample at the measurement electrode by passing through a porous insulating substrate provided with a measurement electrode on at least one surface; and a step of measuring an activity signal of the biological sample via the measurement electrode. This is achieved by the activity signal measurement method of the sample.
- FIG. 1 is a schematic configuration diagram of a main part of an apparatus for measuring an activity signal of a biological sample according to a first embodiment of the present invention.
- FIG. 2 is an enlarged view of a main part of the apparatus shown in FIG.
- Fig. 3 (A) and (B) are schematic diagrams showing the activities of biological samples (cells). You.
- FIG. 4 is a schematic plan view of a biological sample activity signal measuring device according to a second embodiment of the present invention.
- FIG. 5 is (A) a plan view and (B) a cross-sectional view of the cell isolation part of the device shown in FIG.
- FIG. 6 is (A) a plan view and (B) a cross-sectional view of the porous insulating substrate of the device shown in FIG.
- FIG. 7 is a partial sectional view of the device shown in FIG.
- FIG. 8 is another partial cross-sectional view of the device shown in FIG.
- 9 (A) and 9 (B) are block diagrams showing a schematic configuration of a biological sample activity signal measuring device according to a third embodiment of the present invention.
- FIG. 10 is a graph showing the variation of the average value of the standard deviation with respect to Carbacho 1 concentration.
- FIGS. 11 (A) and 11 (B) are block diagrams showing a schematic configuration of a biological sample activity signal measuring apparatus according to a fourth embodiment of the present invention.
- FIG. 12 is a graph showing the result of approximating the variation of the standard deviation before and after administering Carbachol by a normal distribution.
- FIG. 13 is a diagram showing a result of approximating, by a normal distribution, a variation in the standard deviation before and after administering Carbacho 1 obtained by a conventional method.
- FIG. 14 is a diagram showing the amount of separation when the average value and half-value width of the obtained normal distribution are compared with reference values.
- FIG. 15 is a block diagram showing a schematic configuration of a biological sample activity signal measuring device according to another embodiment of the present invention.
- FIG. 16 is a block diagram showing a schematic configuration of an apparatus for measuring an activity signal of a biological sample according to still another embodiment of the present invention.
- FIG. 1 is a schematic diagram of a main part of an apparatus for measuring an activity signal of a biological sample according to a first embodiment of the present invention.
- a measurement electrode 1 for detecting a physicochemical signal of a biological sample such as a cell is formed on an upper surface (a surface on which a biological sample is placed) of a porous insulating substrate 5, and a conductive wire is 2 is derived.
- a physicochemical signal is a signal generated by a biological sample such as a cell, a signal generated from a specific site to be measured, such as a cell ion channel, or a cell channel or receptor that responds to a drug. Such as a signal that changes due to a specific event in the measurement object such as activation of a signal.
- porous insulating substrate 5 a nylon mesh is used in the present embodiment, but is not limited thereto.
- Cellulose mixed ester Ethylene, polycarbonate, polypropylene, polyethylene terephthalate and the like may be used.
- isopore made of polyethylene terephthalate: manufactured by Millipore
- omnipore made of polytetrafluoroethylene: manufactured by Millipore
- a typical example is a pore diameter of 5 and a thickness of 100 m, but a porous insulating substrate having a thickness of 100 m or more can also be suitably used.
- This measuring device is manufactured as follows. First, the measurement electrode 1 and the conductive wire 2 are formed on the porous insulating substrate 5. The formation of the measurement electrode 1 and the conductive wire 2 is preferably performed by sputtering a conductive material. In the present embodiment, gold is used as a conductive material, and high-frequency plasma is generated between a pair of electrodes under low vacuum conditions in the presence of an inert gas such as argon, so that the gold on the cathode is ionized with ion energy. It is flipped and formed on a porous insulating substrate on the opposite anode. The electrodes and the conductive wires can be formed by a vacuum deposition method, a printing method, or the like in addition to the sputtering method.
- the conductive material instead of using gold as the conductive material, platinum, copper, silver, silver and silver chloride, platinum and platinum black may be selected.
- a conductive material made of a conductive plastic can be used.
- the measurement electrode 1 is sputtered, it is preferable to form the electrode material so that the electrode material penetrates deep into the porous insulating substrate 5 without using a mask.
- the conductive wire 2 is patterned by previously covering the porous insulating substrate 5 with a mask (not shown) so as to suppress the penetration of the conductive material into the deep portion of the porous insulating substrate 5.
- the shape of the formed measurement electrode 1 is a disk shape in the present embodiment, but may be any shape according to the measurement target.
- the size of the measuring electrode 1 is not particularly limited, but in the present embodiment, the measuring electrode 1 has a horizontal sectional area substantially equal to the horizontal sectional area of the measuring chamber A described later.
- the porous insulating substrate 5 is sandwiched between the cell isolation part 3 and the support substrate 6.
- the cell isolation part 3 and the support substrate 6 each have an opening, and are arranged such that the centers of the opening of the cell isolation part 3, the measurement electrode 1 of the porous insulating substrate 5 and the opening of the support substrate 6 substantially coincide with each other. You. As a result, a measurement chamber A (corresponding to the entire space of the opening formed in the cell isolation unit 3 in FIG. 1) defined by the opening wall of the cell isolation unit 3 and the porous insulating substrate 5 is formed.
- the cell isolation part 3 and the support substrate 6 are fixed by an adhesive layer 4 made of an adhesive interposed at the periphery of the opening.
- the adhesive layer 4 preferably has easy releasability and water-blocking property, and examples thereof include one-component RTV rubber (deacetic acid type) KE42T (Shin-Etsu Chemical Co., Ltd.).
- a reference electrode 7 is provided on the side wall of the measurement chamber A, and the reference electrode 7 is immersed in the liquid 23 to be measured contained in the measurement chamber A.
- the reference electrode 7 provides a reference potential for detecting an activity signal of a biological sample to be measured, and is composed of, for example, Ag—AgCl.
- a DMEM culture solution can be exemplified as the test solution 23, and animal-derived cells can be exemplified as the cells to be cultured.
- the upper portion of the measurement chamber A is covered with a lid 21, which prevents the liquid 23 to be measured from evaporating.
- the lid 21 may not necessarily be provided depending on the type of the liquid 23 to be measured and the measurement conditions, etc.
- the suction line attachment 8 is fixed to the lower surface side of the support substrate 6 via the adhesive layer 9.
- the suction line attachment 8 is tapered upward from below. It has a suction section 8a that expands and a suction line 8b connected to the suction section 8a, and alignment is performed so that the suction section 8a substantially matches the opening of the support substrate. Will be In this way, a suction chamber B defined by the porous insulating substrate 5, the opening wall of the support substrate 6, and the inner wall of the sucking bow I portion 8a is formed.
- the suction line attachment 8 functions as a transfer device for suctioning and transferring the liquid 23 to be measured, and is connected to a suction pump (not shown) on the suction line 8b. In this way, an activity signal measuring device for a biological sample can be configured.
- a test solution 23 such as a cell culture solution is injected into the measurement chamber A.
- the amount of the liquid 23 to be supplied to the measurement chamber A is, for example, 50 microliters.
- the amount of the liquid 23 to be dropped onto the suction champ B via the porous insulating substrate 5 is very small.
- the quantity of 3 is less than 150.
- a suction pump (not shown) is operated to suck the liquid 23 to be measured in the measurement chamber A.
- the pressure in the suction chamber B is reduced.
- the biological sample 25 such as cells contained in the liquid 23 to be measured cannot pass through the porous insulating substrate 5 and is adsorbed on the measurement electrode 1 as shown in FIG.
- the activity signal generated by the biological sample 25 can be detected as a potential difference generated between the measurement electrode 1 and the reference electrode 7. For example, when the biological sample 25 is a cell, as shown in Fig.
- a cell in a stationary state is generated because the opening and closing of ion channels are in a balanced state, and the change in conductance of each channel is small.
- the voltage change is small, and the amplitude of the potential near the cell membrane becomes substantially uniform.
- active cells have a large change in the generated voltage due to a large change in the conductance of each channel due to the non-equilibrium state of the opening and closing of the ion channels, and the vicinity of the cell membrane.
- the amplitude of the potential becomes non-uniform. Therefore, the activity state of the cell can be determined based on the time-series change of the detected potential difference.
- the inside of the apparatus is cleaned by supplying a cleaning solution such as saline to measurement chamber A while operating a suction pump (not shown).
- a cleaning solution such as saline
- the next liquid 23 to be measured is poured into the measuring chamber A. In this way, for example, an activity signal of a biological sample can be sequentially measured for various solutions containing a compound as a product candidate.
- the biological sample 25 is brought into close contact with the measurement electrode 1 simply by supplying the liquid 23 to be measured to the measurement chamber A and sucking it through the suction line attachment 8.
- the contact resistance can be increased and the signal detection sensitivity can be increased.
- replacement and cleaning of the liquid 23 to be measured can be performed in a short time by the suction line attachment 8.
- the activity signal of the biological sample can be detected easily, quickly and with high accuracy.
- FIG. 4 is a schematic plan view of a biological sample activity signal measuring device according to a second embodiment of the present invention.
- This device is a device in which 16 measurement electrodes 1 in the device of the first embodiment shown in FIG. 1 are arranged in a matrix, and in this embodiment, the diameter of each measurement electrode 1 is 2 mm, and the measurement electrodes 1 are adjacent to each other.
- the distance between measuring electrodes 1 is l mm.
- the number of measuring electrodes 1, arrangement, size, etc. shape but is not limited to this embodiment, a good Masui an example, the area of the measuring electrode 1 1 111 2-1 0
- the shape is almost circular or rectangular, the distance between adjacent measuring electrodes 1 is 10 to: L0000m, and the arrangement is matrix-like.
- the same components as those in the first embodiment are denoted by the same reference numerals, and detailed description will be omitted.
- the measurement electrode 1 and the conductive wire 2 connected to the measurement electrode 1 are arranged on the surface side of the porous insulating substrate 5.
- the porous structure may be destroyed to further enhance the insulating property.
- the reference electrode 7 and the conductive wire 12 connected to the reference electrode 7 are provided on the inner wall and the upper surface of the opening of the cell isolation part 3 corresponding to each measurement electrode 1.
- the cell isolation part 3 is usually made of a transparent material.
- FIG. 5 is a (A) plan view and (B) cross-sectional view of the cell isolation part 3
- FIG. 6 is a (A) plan view and (B) cross-sectional view of the porous insulating substrate 5.
- the measurement chamber A is formed at each opening of the cell isolation section 3 in which a plurality of measurement electrodes (not shown) are respectively arranged.
- the measurement electrode 1 The conductive wire 2 is formed through the mask layer 10 formed on the upper surface of the porous insulating substrate 5 while being formed by impregnating the inside of the porous insulating substrate 5 by sputtering the material without a mask.
- FIG. 7 and 8 are partial cross-sectional views of the device shown in FIG. 4.
- FIG. 7 shows a region C on an enlarged scale
- FIG. 8 shows a region D on an enlarged scale.
- the biological sample 25 such as a cell contained in the liquid 23 to be measured is sucked by the suction line attachment (not shown) to be adsorbed to the measurement electrode 1.
- a plurality of suction portions (corresponding to reference numeral 8a in FIG. 1) of the suction line attachment are provided in correspondence with each measurement electrode 1, and are provided through a common suction line (corresponding to reference numeral 8b in FIG. 1).
- Biological samples 25 can be simultaneously adsorbed to each measurement electrode 1. As a result, the activity signal of the biological sample under various conditions can be measured in a short time. Attachment of the biological sample 25 to each measurement electrode 1 can be performed at different timings by providing individual suction lines for each measurement electrode 1 instead of providing a common suction line.
- FIG. 9 is a block diagram showing a schematic configuration of a biological sample activity signal measuring device according to the third embodiment of the present invention.
- This apparatus has the function of processing the electric signal detected in the measuring section 101 as the measuring section (signal source) 101 in the apparatus according to the first embodiment.
- a unit standard deviation calculation unit 102 calculates the standard deviation using a predetermined number of samples as one unit based on the time series data detected by the measurement unit 101. Each unit containing a predetermined number of samples may be continuous in time, or may be at regular time intervals.
- the average value calculation unit 105 calculates the average value of the obtained plurality of standard deviations.
- the activity evaluation unit 120 evaluates the activity of the biological sample based on the average value of the standard deviation.
- the activity evaluation unit 120 includes an activity calculation unit 108 and an activity classification unit 109, and calculates the activity based on the input information according to the purpose of measurement. The activity can be classified by comparing it with information stored in advance.
- the overnight display section 110 displays the obtained activity on a screen. According to this device, constant Noise can be removed from digital signals (predetermined time-series data) acquired at sampling rates of, for example, to extract, measure, and classify significant signals representing the opening and closing of ion channels.
- the unit standard deviation calculation unit 102, the average value calculation unit 105, and the activity evaluation unit 108 read a hard disk on which a program for executing these calculations is recorded.
- the data display unit 110 can be configured by a built-in computer, and the data display unit 110 can be configured by a CRT.
- the computer further includes a normal distribution approximation unit 103, a stimulus generation unit 104, and a mean / half width calculation unit 106, which will be described later.
- Carbachol is a chemical known to be an analog of the neurotransmitter acetylcholine.
- Carbachol manufactured by Sigma
- Carbachol is dissolved in artificial cerebrospinal fluid and allowed to act on neurons at concentrations of 0, 0.1, 0.3, 1, 3, 10, 30, and 100 M.
- the electrical signals emitted by the cells when they were exposed were measured.
- time-series data every 100 milliseconds was sampled from the time-series data for 10 seconds obtained from the measurement unit 101, and the standard deviation was calculated.
- the result of plotting the average value of the obtained standard deviations is shown in FIG.
- the average value of the standard deviation represents the fluctuation of the potential near the cell membrane, and this value can be used to evaluate the activity of the ion channel.
- the average value of the standard deviation increases as the concentration of Carbacho 1 increases, but the average value of the standard deviation decreases with the peak at 10.
- the measurement method and apparatus according to the present embodiment confirmed that the activity of the ion channel in the mussel neurons was dependent on the concentration of Carbachol. Furthermore, based on the results of this experiment, it is possible to infer the total channel activity of neurons.
- FIG. 11 is a block diagram showing a schematic configuration of a biological sample activity signal measuring device according to a fourth embodiment of the present invention.
- This device as shown in Fig. 11 (B), A configuration similar to that of the third embodiment (see FIG. 9B) is provided.
- the mean value calculation unit 105 in FIG. 9A is not used, and the normal distribution approximation unit 103 and the mean / half-width calculation unit 106 are used, so that the configuration shown in FIG. Is done.
- the normal distribution approximation unit 103 classifies the plurality of standard deviations obtained by the unit standard deviation calculation unit 102 into a plurality of classes set for each predetermined width. Then, this class is set as the X axis, the number of standard deviations classified into each class is plotted on the Y axis, and the obtained graph is approximated to a normal distribution. Methods for approximating the normal distribution include various curve approximation analyses, such as exponential decrease, exponential increase, Gaussian, Lorenz, sigma, multiple peaks, and nonlinearity.
- the average value / half width calculation unit 106 calculates the average value and the half value width (width that is half the peak height) of the obtained normal distribution.
- the action of the chemical substance Carbacho 1 on nerve cells was measured using nerve cells prepared from a mussel as a material.
- the normal distribution approximation unit 103 created the frequency distribution of the standard deviation based on the detection signal of the measurement unit 101 before and after administering 50 M concentration of Carbacho 1 to the neurons of the mussel.
- Fig. 12 shows the result of approximating the normal distribution by creating a histogram using the standard deviation calculated every 5 ms based on the time series data consisting of the detection signals for 10 seconds before and after administering Carb ac ho 1
- the graph on the left shows the state before administration
- the graph on the right shows the state after administration.
- the average value and the half width of the standard deviation were increased by the administration of Carbacho1.
- the average and half-value widths before administration are 0.478 and 0.109, while the average and half-value widths before administration are 0.407 and 0.109. It was 175. This result is considered to indicate that the administration of Carbachol activated the ion channel of the mussel neuron, and the action potential fluctuated due to the opening and closing of the activated channel.
- FIG. 13 shows the results of comparison before and after administration by the conventional intracellular recording method under the same conditions as in the above experiment.
- the measurement method according to the present embodiment is based on the extracellular recording method. However, comparing FIG. 12 and FIG. 13, it can be seen that the same results as in the case of the intracellular recording method were obtained.
- the measurement method of the present invention it is possible to easily measure the cell activity associated with the opening and closing of the ion channel and the change thereof without using the conventional intracellular recording method. Therefore, for example, the electrical change of the biological sample can be measured without forming a high-resistance shield (gigashield) between the biological sample and the measurement device, and the biological sample may be damaged. There is no.
- a high-resistance shield gigashield
- the absolute value of the channel activity and the increase / decrease of the channel activity before and after the administration of the drug to the cells or the dose can be compared.
- Qualitative or quantitative classification can be performed.
- Fig. 14 shows a normal distribution graph of the standard deviation from the detection signal of the measuring unit 101, and the difference between the average value and half-value width of this normal distribution compared to the reference value is the relative shift value. And the results expressed as relative spread.
- the relative movement values and relative spreads to difendipine were stored in advance in a database at various concentrations (0. IMIOOM) as parameters, and the effects of the two Ca channel inhibitors A and B were determined. Classification was performed.
- compound A has a similar behavior of relative migration value and relative spread for each concentration to difludipine ( ⁇ ), and a Ca ion channel similar to difludipine. Presumed to be an inhibitor.
- compound B mouth
- the distance from the reference value is within a predetermined value range (for example, within a circle of ⁇ 5% shown by a broken line in the figure). By judging whether or not this is the case, drug screening can be performed efficiently.
- the evaluation is performed by using the difference amount when the average value and the half width of the normal distribution obtained based on the detection signal are compared with the reference value, respectively.
- the activity may be evaluated by appropriately using a parameter based on the standard deviation (or variance) of the obtained normal distribution.
- the configuration of the fourth and fifth embodiments shown in FIG. 11 (A) may be further provided with a sample distribution unit 1111 to obtain the configuration shown in FIG.
- the sample sorting unit 111 is a very effective means for analyzing the characteristics of each of multiple types of ion channels present on the cell membrane.
- the signal adding unit 107 adds the activity signal generated in the selected one or a plurality of measuring units (signal sources) 101.
- each biological sample can be stimulated at the same time, whereby the timing of a plurality of activity signals to be added is increased. Can be matched.
- the liquid to be measured passes through the porous insulating substrate by providing a suction line attachment and sucking the liquid to be measured.
- the liquid to be measured can be configured to pass through the porous insulating substrate.
- the average value calculation unit calculates the average value based on the plurality of standard deviations calculated by the unit standard deviation calculation unit.
- the plurality of standard deviations may be grouped into a certain number in a time series, and an average value may be calculated for each group.
- the time at which this average value is equal to or higher than a predetermined value and / or the time at which the rate of increase of the average value is equal to or lower than the predetermined value are identified.
- the data may be displayed on the data display unit. This can provide an indication of the time lag before a chemical substance affects cell activity. Industrial applicability
- an activity signal measurement device and a measurement method for a biological sample capable of easily, quickly, and accurately detecting an activity signal emitted from the biological sample.
- the present invention is applicable to, for example, high-speed drug screening, cytodiagnosis (for example, discrimination between cancer cells and normal cells), and can be carried out on-site at the time of surgery or the like.
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Description
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Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
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JP2004503946A JP3624292B2 (ja) | 2002-05-13 | 2003-05-08 | 生体試料の活動信号計測装置および計測方法 |
AU2003234787A AU2003234787A1 (en) | 2002-05-13 | 2003-05-08 | Instrument and method for measuring action signal of biological sample |
US10/678,138 US7172860B2 (en) | 2002-05-13 | 2003-10-06 | Apparatus and method for measuring activity signals of biological samples |
US11/652,605 US7594984B2 (en) | 2002-05-13 | 2007-01-12 | Apparatus and method for measuring activity signals of biological samples |
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JP2002137819 | 2002-05-13 | ||
JP2002/137819 | 2002-05-13 |
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US10/678,138 Continuation US7172860B2 (en) | 2002-05-13 | 2003-10-06 | Apparatus and method for measuring activity signals of biological samples |
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WO2003096002A1 true WO2003096002A1 (fr) | 2003-11-20 |
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PCT/JP2003/005735 WO2003096002A1 (fr) | 2002-05-13 | 2003-05-08 | Instrument et procede de mesure du signal d'action d'un echantillon biologique |
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US (2) | US7172860B2 (ja) |
JP (1) | JP3624292B2 (ja) |
CN (1) | CN100370247C (ja) |
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WO (1) | WO2003096002A1 (ja) |
Cited By (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2007215473A (ja) * | 2006-02-16 | 2007-08-30 | Foundation For The Promotion Of Industrial Science | 培養細胞の電気シグナル計測デバイスおよび該デバイスを用いる電気シグナル計測方法 |
JP2008122250A (ja) * | 2006-11-13 | 2008-05-29 | Katsumasa Ogawa | 路面状況判定方法 |
WO2019027216A1 (ko) * | 2017-07-31 | 2019-02-07 | 재단법인대구경북과학기술원 | 미세동물의 생체신호 측정을 위한 트랩유닛을 구비한 생체신호측정기 및 이를 이용한 미세동물의 생체신호 측정방법 |
US11320348B2 (en) | 2015-12-30 | 2022-05-03 | Ventana Medical Systems, Inc. | System and method for real time assay monitoring |
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CN100370247C (zh) * | 2002-05-13 | 2008-02-20 | 松下电器产业株式会社 | 生物样本的活动信号测量装置和测量方法 |
CN100372920C (zh) * | 2003-06-27 | 2008-03-05 | 松下电器产业株式会社 | 药理测定装置及系统以及其中使用的井容器 |
JP4174590B2 (ja) * | 2004-02-17 | 2008-11-05 | 独立行政法人産業技術総合研究所 | 区画アレイ型細胞外電位測定プローブ |
CN107271493A (zh) * | 2017-07-07 | 2017-10-20 | 中国电建集团中南勘测设计研究院有限公司 | 一种基于正态分布的水流掺气浓度计算方法及系统 |
US20220276268A1 (en) * | 2019-07-09 | 2022-09-01 | The Regents Of The University Of California | Automated rapid on-site evaluation machine and stain |
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Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2007215473A (ja) * | 2006-02-16 | 2007-08-30 | Foundation For The Promotion Of Industrial Science | 培養細胞の電気シグナル計測デバイスおよび該デバイスを用いる電気シグナル計測方法 |
JP2008122250A (ja) * | 2006-11-13 | 2008-05-29 | Katsumasa Ogawa | 路面状況判定方法 |
US11320348B2 (en) | 2015-12-30 | 2022-05-03 | Ventana Medical Systems, Inc. | System and method for real time assay monitoring |
US11854196B2 (en) | 2015-12-30 | 2023-12-26 | Ventana Medical Systems, Inc. | System and method for real time assay monitoring |
WO2019027216A1 (ko) * | 2017-07-31 | 2019-02-07 | 재단법인대구경북과학기술원 | 미세동물의 생체신호 측정을 위한 트랩유닛을 구비한 생체신호측정기 및 이를 이용한 미세동물의 생체신호 측정방법 |
KR20190013129A (ko) * | 2017-07-31 | 2019-02-11 | 재단법인대구경북과학기술원 | 미세동물의 생체신호 측정을 위한 트랩유닛을 구비한 생체신호측정기 및 이를 이용한 미세동물의 생체신호 측정방법 |
KR101994341B1 (ko) * | 2017-07-31 | 2019-07-08 | 재단법인대구경북과학기술원 | 동물의 생체신호 측정을 위한 트랩유닛을 구비한 생체신호측정기 및 이를 이용한 동물의 생체신호 측정방법 |
Also Published As
Publication number | Publication date |
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JPWO2003096002A1 (ja) | 2005-09-15 |
US7594984B2 (en) | 2009-09-29 |
CN1633595A (zh) | 2005-06-29 |
CN100370247C (zh) | 2008-02-20 |
US20040106139A1 (en) | 2004-06-03 |
US7172860B2 (en) | 2007-02-06 |
US20070134651A1 (en) | 2007-06-14 |
JP3624292B2 (ja) | 2005-03-02 |
AU2003234787A1 (en) | 2003-11-11 |
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