Source: http://www.google.com/patents/US20040096928?dq=6966484
Timestamp: 2016-07-26 12:53:32
Document Index: 604549507

Matched Legal Cases: ['Application No. 2000', 'art 4', 'art 4', 'art 11', 'art) 26', 'art 4', 'art 11', 'art 30', 'art 30', 'art 30', 'art 30', 'art 11', 'art 12', 'art 30', 'art 30']

Patent US20040096928 - Biosensor - Google PatentsSearch Images Maps Play YouTube News Gmail Drive More »Sign inPatentsIn a biosensor comprising an insulating base plate, an electrode system including a measuring electrode and a counter electrode provided on said base plate, a cover for covering said insulating base plate, at least one reaction layer containing oxidoreductase and/or an electron mediator, a sample solution...http://www.google.com/patents/US20040096928?utm_source=gb-gplus-sharePatent US20040096928 - BiosensorAdvanced Patent SearchPublication numberUS20040096928 A1Publication typeApplicationApplication numberUS 10/472,075PCT numberPCT/JP2002/011809Publication dateMay 20, 2004Filing dateNov 12, 2002Priority dateNov 14, 2001Also published asCN1489690A, EP1452857A1, EP1452857A4, US6977032, WO2003042680A1Publication number10472075, 472075, PCT/2002/11809, PCT/JP/2/011809, PCT/JP/2/11809, PCT/JP/2002/011809, PCT/JP/2002/11809, PCT/JP2/011809, PCT/JP2/11809, PCT/JP2002/011809, PCT/JP2002/11809, PCT/JP2002011809, PCT/JP200211809, PCT/JP2011809, PCT/JP211809, US 2004/0096928 A1, US 2004/096928 A1, US 20040096928 A1, US 20040096928A1, US 2004096928 A1, US 2004096928A1, US-A1-20040096928, US-A1-2004096928, US2004/0096928A1, US2004/096928A1, US20040096928 A1, US20040096928A1, US2004096928 A1, US2004096928A1InventorsMiwa Hasegawa, Tomohiro Yamamoto, Shin Ikeda, Toshihiko YoshiokaOriginal AssigneeMiwa Hasegawa, Tomohiro Yamamoto, Shin Ikeda, Toshihiko YoshiokaExport CitationBiBTeX, EndNote, RefManPatent Citations (3), Referenced by (21), Classifications (8), Legal Events (5) External Links: USPTO, USPTO Assignment, EspacenetBiosensor
BRIEF DESCRIPTION OF DRAWINGS [0021] [0021]FIG. 1 is a perspective view of a disassembled biosensor according to an embodiment of the present invention. [0022] [0022]FIG. 2 is a perspective view of an assembled biosensor according to an embodiment of the present invention. [0023] [0023]FIG. 3 is a schematic vertical section of the sensor excluding a reaction layer and the like. [0024] [0024]FIG. 4 is a schematic vertical section illustrating the vicinity of an electrode system of the sensor. [0025] [0025]FIG. 5 is a graph illustrating a response characteristic of a cholesterol sensor according to an example of the present invention. BEST MODE FOR CARRYING OUT THE INVENTION [0026] As described above, the biosensor according to the present invention includes an electrode system and a reaction layer and has a filter for filtering hemocytes provided between a sample solution supply pathway having an air aperture on a terminal end side and a sample solution supply part. Plasma from which hemocytes are removed by the filter is sucked into the sample solution supply pathway due to capillarity. The biosensor is characterized in that a top face and an end face of a primary side portion of the filter are exposed and a sample solution supply part is provided, to which a sample solution is temporarily supplied. [0027] Further, the biosensor of the present invention is characterized in that a rail is provided from the sample solution supply part to the filter so that the sample solution is concentrated at the top and end faces of the filter. [0028] With the above-described structure, most of the sample solution is efficiently introduced to the filter without reducing the amount of the sample solution that can be sucked within a certain period of time, which allows supplying the filtrate rapidly to the sample solution supply pathway. In particular, the biosensor of the present invention is easy to use in the measurement involving the blood collection by fingertip centesis since whole blood on the fingertip can be rubbed against the sensor with ease and efficiency. [0029] The electron mediator used in the present invention may be selected from, besides potassium ferricyanide, redox compounds having electron transferring ability to and from oxidoreductase such as cholesterol oxidase. [0030] Oxidoreductase is an enzyme of which the substrate is a measuring object. In a sensor whose measuring object is glucose, glucose oxidase is used. In order to measure a cholesterol value in serum, which is used as a diagnostic index, are used cholesterol oxidase or cholesterol dehydrogenase which is an enzyme for catalyzing oxidative reaction of cholesterol and cholesterol esterase which is an enzyme for catalyzing a process of converting cholesterol ester into cholesterol. Since the enzyme reaction of cholesterol esterase proceeds very slowly, an appropriate surfactant may be added, for example, to improve the activity of cholesterol esterase and reduce the time required for the whole reaction. [0031] A layer containing the electron mediator and a reaction layer containing oxidoreductase are arranged on or in the vicinity of the electrode system in the sensor. In a sensor including a covering member, which is combined with the base plate having the electrode system provided thereon to form therebetween a sample solution supply pathway for supplying a sample solution to the electrode system, the reaction layer may be arranged on a portion exposed to the sample solution supply pathway or an opening of the sample solution supply pathway. In either position, it is preferred that the reaction layer is easily dissolved by the introduced sample solution to reach the electrode system. [0032] For the purpose of protecting the electrodes and inhibiting the reaction layer to be formed from peeling, a hydrophilic polymer layer is preferably formed on the electrode system. Other than on the electrode system, the hydrophilic polymer layer is preferably formed as a base for forming the reaction layer or a hydrophilic polymer may be contained in the reaction layer lying at the bottom. [0033] Above all, it is preferable that the reaction layer containing the electron mediator is separated from the surfactant to enhance the solubility of the reaction layer. It is also preferable that the electron mediator is separated from cholesterol oxidase and cholesterol esterase, which are enzymes for catalyzing the oxidative reaction of cholesterol, in view of stability during storage. [0034] There is an example of a biosensor for measuring blood sugar level in which a lipid-containing layer is formed to cover the layers formed on the electrode system such that the sample solution is introduced to the reaction layer (for example, Japanese Laid-Open Patent Publication No. HEI 2-062952). In the biosensor according to the present invention for measuring cholesterol, it is preferred that part of the reaction layer is formed by a freeze drying method (e.g., the specification of Japanese Patent Application No. 2000-018834) or the surface of the covering member is given hydrophilicity by means of a surfactant or plasma irradiation. Such a structure can eliminate the need of forming the lipid layer. [0035] As the hydrophilic polymer, for example, may be used water-soluble cellulose derivatives, in particular ethyl cellulose, hydroxypropyl cellulose, carboxymethyl cellulose, polyvinylpyrrolidone, polyvinyl alcohol, gelatin, agarose, polyacrylic acid or salts thereof, starch or derivatives thereof, polymers of maleic anhydride or salts thereof, polyacrylamide, methacrylate resin and poly-2-hydroxyethyl methacrylate. [0036] As the surfactant, for example, may be used n-octyl-β-D-thioglucoside, polyethylene glycol monododecyl ether, sodium cholate, dodecyl-β-maltoside, sucrose monolaurate, sodium deoxycholate, sodium taurodeoxycholate, N,N-bis(3-D-gluconamidopropyl)deoxycholamide and polyoxyethylene (10) octyl phenyl ether. [0037] In the case of using lipid, amphipathic phospholipid such as lecithin, phosphatidyl choline and phosphatidylethanolamine is favorably used. [0038] An oxidation current may be measured by a measurement method on a two-electrode system using only a measuring electrode and a counter electrode or a three-electrode system using a reference electrode in addition, among which the three-electrode system allows measurement with greater accuracy. [0039] Hereinafter, the present invention will be detailed by way of specific embodiments with reference to the figures. FIG. 1 is a perspective view of a disassembled biosensor according to a preferred embodiment of the present invention. [0040] In the biosensor shown in FIG. 1, an electrode system including a working electrode 2 and a counter electrode 3 is formed by sputtering using palladium and subsequent laser trimming on the left side of an insulating base plate 1 made Of insulating resin such as polyethylene terephthalate. An area of the electrodes is determined in correspondence with a width of a slit 12 formed in a spacer 7 to be described later. The insulating base plate 1 also includes an adhesive part 4 and an aperture 5. The adhesive part 4 may be provided by applying, for example, a double-stick tape on the insulating base plate 1. [0041] The spacer 7 is provided with an opening 10 for accommodating a filter 6 therein, a slit 12 for forming a sample solution supply pathway 12′, rails 9 formed on both sides of the slit 12 to introduce a sample solution into a primary side portion of the filter and a connecting part 11 for connecting the opening 10 and the slit 12. [0042] A cover 13 includes an air aperture 17, an opening 16 and rails 15 formed on both sides of the opening 16 to introduce the sample solution into the primary side portion of the filter. [0043] A spacer 18 includes an opening 21 for accommodating the filter 6 therein and rails 20 formed on both sides of the opening 21 to introduce the sample solution into the primary side portion of the filter. [0044] A cover 22 includes an opening 25 for accommodating the filter 6 therein, a pressing part (dividing part) 26, an aperture 27 and rails 24 formed on both sides of the opening 25 to introduce the sample solution into the primary side portion of the filter. [0045] Upon integrating the members shown in FIG. 1, the opening 10 in the spacer 7, the opening 16 in the cover 13, the opening 21 in the spacer 18 and the opening 25 in the cover 22 shown in FIG. 1 are communicated. Further, a second air aperture 31 in the insulating base plate 1, a terminal end of the slit 12 in the spacer 7 and the first air aperture 17 in the cover 13 are communicated. [0046] The filter 6 is made of glass fiber filter paper and has an isosceles triangle shape as viewed in a projection on a plane identical to the insulating base plate 1 shown in FIG. 1. [0047] In assembling the sensor, first, the cover 13 is placed on the spacer 7 in a positional relationship as indicated by dashed lines in FIG. 1 to obtain a joint base plate A. At this time, the slit 12 forms a concave portion in the cover 13 and the spacer 7 thus jointed, in which a reaction layer is formed as described later. [0048] Then, the cover 22 is placed on the spacer 18 in a positional relationship as indicated by dashed lines in FIG. 1 to obtain a joint base plate B. [0049] Further, the insulating base plate 1 and the joint base plates A and B are assembled in a positional relationship as indicated by dashed lines in FIG. 1 and the filter 6 is mounted thereon in such a manner that the filter 6 having an almost isosceles triangle shape in a projection on a plane identical to the insulating base plate 1 contacts the adhesive part 4 of the insulating base plate 1 at the right end on the primary side (bottom side). [0050] In other words, the right end on the primary side (bottom side) of the filter 6 enters a state of being disposed on the insulating base plate 1 and fitted into the opening 10 of the spacer 7, the opening 16 of the cover 13, the opening 21 of the spacer 18 and the opening 25 of the cover 22. The left end on a secondary side (vertex side) of the filter 6 is brought into a state of being sandwiched between the connecting part 11 in the concave portion of the joint base plate A and the insulating base plate 1. [0051] [0051]FIG. 2 shows a schematic perspective view of the thus obtained biosensor according to the present invention and FIG. 3 shows its structure in section. FIG. 3 is a schematic vertical section of the biosensor according to the present invention taken along the line X-X shown in FIG. 2. In FIG. 3, reaction layers and the like provided in the sample solution supply pathway 12′ are omitted. [0052] In the biosensor of the present invention shown in FIGS. 1 to 3, apertures 5 and 27 are formed as shown in FIG. 3, in which the filter 6 is not in contact with the other members. [0053] That is, the biosensor of the present invention includes, as shown in FIG. 3, a first pressing part a for holding the primary side portion of the filter 6 from the bottom, second pressing parts b and b′ for holding the secondary side portion of the filter 6 from the top and the bottom and a third pressing part c for holding the center of the filter 6 from the top. [0054] Between the second pressing parts b and b′ and the third pressing part c, the apertures 5 and 27 are communicated via the openings 10, 16 and 21 (see FIG. 1) to make the filter 6 not contact the other members. [0055] Further, opening ends 8, 14, 19 and 23 shown in FIG. 1 are also communicated to form a concave portion which serves as a sample solution supply part 30 as shown in FIG. 2. In the biosensor of the present invention, the existence of the concave portion makes an end face of the sensor open (open to the outside). Therefore, as a method of adding the sample solution, for example, a fingertip stung to bleed may be rubbed against the sample solution supply part 30. The sample solution is temporarily held in the concave portion and then supplied rapidly and intensively to the primary side of the filter. [0056] [0056]FIG. 4 shows a schematic vertical section illustrating another embodiment of the biosensor of the present invention. The reaction layers and the electrode system omitted in FIG. 2 are depicted in FIG. 4. On the electrode system (2 and 3) of the insulating base plate 1, a hydrophilic polymer layer 28 and a reaction layer 29 are formed. In addition, a reaction layer 30 is formed on the underside of the cover 13 corresponding to a ceiling of the sample solution supply pathway 12′. Other members shown in FIG. 4 are the same as those shown in FIG. 3. [0057] The biosensor shown in FIGS. 1 to 4 is made of six members including the filter and various base plates for easy explanation of the structure. However, the cover 22 and the spacer 18 or the cover 13 and the spacer 7 may be formed as a single member. [0058] In measuring cholesterol in blood with this sensor, whole blood is supplied from the sample solution supply part 30, the concave portion, to the filter 6. At this time, since the spacer 7, the cover 13, the spacer 18 and the cover 22 contact the sample solution supply part 30 at the rails 9, 15, 20 and 24, the whole blood is efficiently supplied to the filter 6. [0059] The supplied blood permeates into the filter 6 from the end face and the top face on the primary side. In the filter 6, since the permeation rate of hemocytes is lower than that of plasma which is a liquid component, the plasma seeps from the tip of the filter 6 on the secondary side. The seeped plasma fills the vicinity of the electrode system and the entire sample solution supply pathway 12′ extending to the connecting part between the first and second air apertures 17 and 31 while dissolving the reaction layer carried on a position covering the electrode system and/or the underside of the cover 13. [0060] Once the entire sample solution supply pathway 12′ is filled up, the liquid flow in the filter 6 stops. At this time, the hemocytes remain in the filter 6 without reaching the secondary side end of the filter 6. It is therefore necessary to design the filter 6 to give a difference in flow resistance between the plasma and the hemocytes to such an extent that the hemocytes do not reach the secondary side end of the filter 6 even if the plasma are passed in an amount enough to fill the sample solution supply pathway 12′. [0061] A depth filter having a pore diameter of 1 to 7 μm is suitably used as the filter of the present invention. The thickness of the filter is preferably 300 to 400 μm. [0062] Through the process of hemocyte filtration, a chemical reaction occurs between the reaction layer dissolved by the plasma and a component to be measured in the plasma (cholesterol in using a cholesterol sensor). After an elapse of a predetermined time, a current value is measured by electrode reaction to determine the quantity of the component in the plasma. [0063] [0063]FIG. 4 shows an example of how the reaction layers are arranged in the vicinity of the electrode system in the sample solution supply pathway 12′. On the electrode system on the insulating base plate 1, are formed a hydrophilic polymer layer 28 containing sodium salt of carboxymethyl cellulose (hereinafter simply referred to as “CMC”) and a reaction layer 29 containing a reaction reagent such as an electron mediator. In the sample solution supply pathway 12′ formed by combining the cover 13 and the spacer 7, a reaction layer 30 containing oxidoreductase is formed on the surface of the cover 13 exposed to the sample solution supply pathway 12′. [0064] As shown in FIGS. 1 to 4, in the sample solution supply pathway 12′, a distance in a direction vertical to the liquid flow is made smaller than the thickness of the primary side portion of the filter 6, whereas a portion of 1 mm from the secondary side end of the filter 6 is compressed to be positioned in the vicinity of the connecting part 11 of the sample solution supply pathway 12′. [0065] The compressed portion of the filter 6 preferably occupied about 1 mm from the filter tip on the secondary side with respect to suction power of a sensor sized as described in the following Example of the present invention. The secondary side portion of the filter 6 was preferably compressed to such a degree that the secondary side portion becomes about � to ⅓ of the primary side portion. [0066] Although it is difficult to express the suction power of the sensor by a numeric value, favorable measurement result (flow rate) was obtained when the spacer 7 is 100 μm in thickness and the filter was compressed to a thickness of 370 μm. The flow rate was low where the filter thickness was 310 μm or less. [0067] Thus, with the sample solution supply pathway 12′ formed smaller than the primary side portion of the filter 6 in unit area in cross section, plasma from which hemocytes are removed by the filter 6 is sucked rapidly into the sample solution supply pathway 12′ due to capillarity. [0068] In general, the reaction layer is easy to dissolve in one portion and hard to dissolve in other portion. The easy-to-dissolve portion lies along the edge of the sample solution supply part 12′, i.e., along the wall surface of the slit 12 of the spacer 7. The hard-to-dissolve portion is a center portion of the reaction layer in the liquid flow direction. Since the sample solution having passed the filter 6 flows along the slit 12 by priority, the sample solution may fill the air aperture in some cases before the center portion of the reaction layer dissolves completely. With the secondary side portion of the filter 6 shaped such that a center thereof is projected inside of the sample solution supply pathway 12′ as compared with the right and left, the sample solution flows along the center portion of the sample solution supply pathway 12′ by priority. Thereby, the plasma can rapidly be flown into the sensor without leaving bubbles in the center portion of the sample solution supply pathway 12′. [0069] In measurement, a fingertip stung to bleed is placed on the sample solution supply part 30 to supply blood to the filter 6. The blood permeates into the filter 6 from the end face and the top face on the primary side. At this time, with the existence of the third pressing part c serving as a partition, the blood does not travel on the surface of the filter 6 by priority to flow directly into the sample solution supply pathway 12′. Further, since the third and first pressing parts c and a do not agree in position as viewed in a projection on a plane identical to the insulating base plate 1, the expansion of the filter 6 is not inhibited and the possibility of destroying the hemocytes is eliminated. [0070] The electrode system is preferably made of noble metal electrodes. If printed electrodes formed by screen printing are used, accuracy in determining the electrode area becomes poor because the preferable width of the sample solution supply pathway 12′ is 1.5 mm or less. On the other hand, the noble metal electrodes allow trimming with laser of 0.1 mm width, which is highly accurate in determining the electrode area. [0071] Hereinafter, an example of the present invention is described, but the invention is not limited thereto. EXAMPLE [0072] A cholesterol sensor configured as shown in FIGS. 1, 2 and 4 was fabricated in the following manner. An electron mediator was contained in a reaction layer 29 and cholesterol oxidase, cholesterol esterase and a surfactant were contained in a reaction layer 29′. [0073] First, 5 μl of 0.5 wt % CMC aqueous solution was dropped onto the electrode system of the insulating base plate 1 and dried in a warm-air dryer at 50� C. for 10 minutes to form a hydrophilic polymer layer 28. [0074] Then, 4 μl of potassium ferricyanide aqueous solution (corresponding to 70 mM of potassium ferricyanide) was dropped onto the hydrophilic polymer layer 28 and dried in the warm-air drier at 50� C. for 10 minutes to form a reaction layer 29 containing potassium ferricyanide. Further, to a solution dissolved therein cholesterol oxidase derived from Nocardia (EC1.1.3.6: ChOD) and cholesterol esterase derived from Pseudomonas (EC.3.1.1.13: ChE), polyoxyethylene (10) octyl phenyl ether (Triton X-100) was added as a surfactant. [0075] The resulting mixture solution was dropped in an amount of 0.4 μl onto a portion of the cover 13 exposed to the sample supply solution pathway 12′, preliminarily frozen with liquid nitrogen at −196� C., and then dried using a freeze dryer for 2 hours to form a reaction layer 30 containing 450 U/ml of cholesterol oxidase, 1125 U/ml of cholesterol esterase and 2 wt % of a surfactant. [0076] Glass fiber filter paper of about 300 to 400 μm thick was stamped into the form of an isosceles triangle having a bottom of 3 mm and a height of 5 mm and a tip thereof on the secondary side was rounded to obtain a filter 6. The filter 6 of an almost isosceles triangle shape was disposed between the insulating base plate 1 and the joint base plate A. [0077] Thereafter, the member obtained by disposing the filter 6 between the insulating base plate 1 and the joint base plate A was bonded to the joint base plate B obtained by integrating the spacer 18 and the cover 22, thereby forming a cholesterol sensor configured as shown in FIGS. 1, 2 and 4. [0078] In this sensor, 10 μl of whole blood sample solutions varied in concentration were added to the sample solution supply part 30. Three minutes later, a pulse voltage of +0.2V with reference to the counter electrode was applied to the measuring electrode, i.e., in the anode direction, and then 5 seconds later, a current value between the measuring electrode and the counter electrode was measured. The results are shown in FIG. 5, which is a graph illustrating a relationship between the cholesterol concentration in the whole blood and the current value. [0079] As apparent from FIG. 5, the sensor of the present invention gives favorable linearity between the cholesterol concentration and the current value. INDUSTRIAL APPLICABILITY [0080] According to the present invention, in the measurement involving the blood collection by fingertip centesis, whole blood on the fingertip is easily rubbed against the sensor with efficiency. Further, hemocytes, which are interfering substances, are removed by the filter without dissolving the hemocytes and the filtrate can rapidly be supplied to the electrode system. Thus, the present invention provides an electrochemical biosensor of excellent response characteristic. Patent CitationsCited PatentFiling datePublication dateApplicantTitleUS5437999 *Feb 22, 1994Aug 1, 1995Boehringer Mannheim CorporationElectrochemical sensorUS6315738 *Dec 30, 1999Nov 13, 2001Terumo Kabushiki KaishaAssembly having lancet and means for collecting and detecting body fluidUS6436255 *Jan 19, 2001Aug 20, 2002Matsushita Electric Industrial Co., Ltd.Biosensor* Cited by examinerReferenced byCiting PatentFiling datePublication dateApplicantTitleUS7727467Jun 18, 2004Jun 1, 2010Roche Diagnostics Operations, Inc.Reagent stripe for test stripUS7749437Jul 6, 2010Roche Diagnostics Operations, Inc.Method and reagent for producing narrow, homogenous reagent stripesUS7829023Jun 18, 2004Nov 9, 2010Roche Diagnostics Operations, Inc.Test strip with vent openingUS7879618Feb 1, 2011Roche Diagnostics Operations, Inc.Method and reagent for producing narrow, homogenous reagent stripsUS7892849Feb 20, 2009Feb 22, 2011Roche Diagnostics Operations, Inc.Reagent stripe for test stripUS8071030Dec 6, 2011Roche Diagnostics Operations, Inc.Test strip with flared sample receiving chamberUS8119414Sep 15, 2010Feb 21, 2012Roche Diagnostics Operations, Inc.Test strip with slot vent openingUS8142721Sep 23, 2010Mar 27, 2012Roche Diagnostics Operations, Inc.Test strip with slot vent openingUS8148164Dec 30, 2009Apr 3, 2012Roche Diagnostics Operations, Inc.System and method for determining the concentration of an analyte in a sample fluidUS8211379Sep 20, 2011Jul 3, 2012Roche Diagnostics Operations, Inc.Test strip with slot vent openingUS8222044Nov 16, 2011Jul 17, 2012Roche Diagnostics Operations, Inc.Test strip with flared sample receiving chamberUS8287703Sep 25, 2008Oct 16, 2012Roche Diagnostics Operations, Inc.Biosensor and method of makingUS8298828Oct 30, 2012Roche Diagnostics Operations, Inc.System and method for determining the concentration of an analyte in a sample fluidUS8551308Sep 25, 2008Oct 8, 2013Roche Diagnostics Operations, Inc.Biosensor and method of makingUS8586373Oct 24, 2012Nov 19, 2013Roche Diagnostics Operations, Inc.System and method for determining the concentration of an analyte in a sample fluidUS8617367 *May 3, 2007Dec 31, 2013Bayer Healthcare LlcElectrochemical test sensor with reduced sample volumeUS8679853Jul 3, 2007Mar 25, 2014Roche Diagnostics Operations, Inc.Biosensor with laser-sealed capillary space and method of makingUS8845869 *Sep 21, 2011Sep 30, 2014Bionime CorporationElectrochemical sensor stripUS9304099Nov 1, 2013Apr 5, 2016Ascensia Diabetes Care Holdings AgElectrochemical test sensor with reduced sample volumeUS20090071847 *May 3, 2007Mar 19, 2009Edelbrock Andrew JElectrochemical test sensor with reduced sample volumeUS20120073966 *Sep 21, 2011Mar 29, 2012Bionime CorporationElectrochemical sensor strip* Cited by examinerClassifications U.S. Classification435/25International ClassificationC12Q1/00, G01N33/49Cooperative ClassificationG01N33/491, G01N27/3272, C12Q1/001European ClassificationG01N27/327B1, C12Q1/00BLegal EventsDateCodeEventDescriptionSep 17, 2003ASAssignmentOwner name: MATSUSHITA ELECTRIC INDUSTRIAL CO., LTD., JAPANFree format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:HASEGAWA, MIWA;YAMAMOTO, TOMOHIRO;IKEDA, SHIN;AND OTHERS;REEL/FRAME:014938/0001;SIGNING DATES FROM 20030728 TO 20030731Jul 4, 2006CCCertificate of correctionJun 29, 2009REMIMaintenance fee reminder mailedDec 20, 2009LAPSLapse for failure to pay maintenance feesFeb 9, 2010FPExpired due to failure to pay maintenance feeEffective date: 20091220RotateOriginal ImageGoogle Home - Sitemap - USPTO Bulk Downloads - Privacy Policy - Terms of Service - About Google Patents - Send FeedbackData provided by IFI CLAIMS Patent Services