Analytical Device and Method Utilizing a Piezoelectric Crystal Biosensor

1. Field of the Invention

The present invention relates to an analytical device and a method for the analysis of biochemicals, microbes and cells utilizing a piezoelectric crystal biosensor.

2. Description of the Prior Art

Various methods for the determination of biochemicals, microbes and cells have included liquid chromatography, electrophoresis, direct observation of agglutination with the naked eyes, and other analytical methods, applying amplification with enzymes, fluorescence chemicals and radio isotopes (EIA, FIA, RIA).

Particularly, for the detection a pathogenic microorganism, a conventional method is comprised adding an antibody solution drop to a microbial suspension and observing the agglutination with the naked eye by using an agglutination plate. Recently, a system for the judgement of the agglutination has been developed, employing an image processing system equipped with a microscope. Further, a method applied to electrochemical determination and immuno reaction has been known. In this method, a microorganism is bound to an antibody immobilized on an organic film and the aimed concentration thereof is determined by measuring a change in the membrane potential.

On the other hand, for immunoassay, a surface acoustic wave (SAW) device has been developed, and one saw device is reported in the following document: J. E. Roederer and G. J. Bastiaans, Anal. Chem. 1983, 55, 2333-2336. This reference discloses that the determination of human IgG is carried out by promoting specific adsorption between immobilized goat anti-human IgG and human IgG at the surface of SAW device. The problem in the above methods, especially in agultination methods, are that the aggultination judged with the naked eye requires those skilled in the art. In addition, these methods give a poor quantitative result and can be hardly automated.

Furthermore, these conventional methods have some disadvantages in that they give poor sensitivity and require troublesome operation.

The image processing system has a large scale and requires considerable cost. The method, utilizing membrane potential, requires troublesome operations and can be hardly automated.

The other methods, for the immunoassay such as EIA, FIA and RIA, although they have a good sensitivity, require, also, troublesome operations.

The SAW device, for human IgG, only has a roughly determination range of human IgG: 0.0225-2.25 mg/ml.

The present invention has made it possible to detect biochemical substances such as biochemicals, microbes and cells and to determine the concentration of the same by the method of immobilizing biochemicals or organic compounds on the surface of the electrode of piezoelectric crystal to modify the surface, specifically conducting binding reaction of the biochemicals or organic compounds with biochemicals to cause weight change on the electrode surface of piezoelectric crystal, and measuring the resonant frequency change induced by the weight change.

It is, therefore, an object of the present invention to provide a piezoelectric crystal biosensor, which can detect biochemicals microbes and cells, in particular pathogenic microorganisms, and to selectively determine the concentration of the same.

Another object of the invention is to provide high sensitive determination method for the piezoelectric crystal biosensor.

A further object of the invention is to provide an improved piezoelectric crystal biosensor, which can analyze the constituents of biochemicals.

In accordance with the method of the present invention, the measuring system utilizing a piezoelectric crystal biosensor has high sensitivity and short operation time. This method has merits such as inexpensive cost automatical operation and repeated analysis.

The above and further objects and novel features of the invention will more fully appear from the following detailed description when the same is read in connection with the accompanying drawings. It is to be expressly understood, however, that the drawings are for purpose of illustration only and is not intended as a definition of the limits of the invention.

FIG. 1 is a perspective view of the entire construction of the piezoelectric crystal biosensor;

FIG. 2 is a sectional view of the piezoelectric crystal biosensor taken along line I-I' of FIG. 1;

FIG. 3 is a block diagram of the measurement system for the piezoelectric crystal biosensor;

FIG. 4 is a graph showing the correlation of Candida (C. albicans) concentration and frequency change of the piezoelectric crystal biosensor;

FIG. 5 is a graph showing the correlation of Saccharomyces (S. cerevisiae) concentration and frequency change of the piezoelectric crystal biosensor;

FIG. 6 is a perspective view of a biosensor and a cell;

FIG. 7 is a block diagram of the entire biosensor system;

FIG. 8 is a graph showing the correlation of human IgG concentration and frequency change;

FIG. 9 and FIG. 10 show the principle of examples 3 and 4, respectively;

FIG. 11 shows the principle of example 5;

FIG. 12(a) is a graph showing the resonant frequency before and after the reaction with mouse .gamma.-globulin;

FIG. 12(b) is a graph showing the relation between each pH of buffer solution and the difference of the resonant frequency;

FIG. 13 shows difference of the resonant frequency for the analysis of the constituents of human IgG;

FIG. 14 is a perspective view of AT-cut piezoelectric crystals and a cell for use in the analysis of biochemicals;

FIG. 15 is a perspective view of GT-cut piezoelectric crystals and a cell for use in the analysis of biochemicals;

FIG. 16 is a block diagram of the determination system for multi analysis.

The present invention has made it possible to detect a microorganism, in particular a pathogenic one, and to determine the concentration of the same by immobilizing an antibody on the surface of a piezoelectric crystal biosensor, specifically binding the antibody to a microorganism to thereby cause a weight change on the surface of electrodes of the piezoelectric crystal biosensor, and measuring the change or shift in the resonant frequency of the piezoelectric crystal biosensor induced by the above weight change.

The amount of microorganisms bound to an immobilized antigen through an antigen-antibody reaction in a definite time, depends on the concentration of the microorganism. Thus the resonant frequency change of the piezoelectric crystal biosensor depends on the concentration of the microorganism.

The piezoelectric crystal of a known resonant frequency is immersed in a microbial suspension or sample liquid to thereby promote an antigen-antibody reaction, and then the resonant frequency is measured again. Thus the concentration of the microorganism can be determined from the resonant frequency change based on a calibration curve which is previously obtained.

Accordingly, the piezoelectric crystal biosensor of the present invention has made it possible to detect a microorganism and to determine the concentration of the same.

Referring to the drawings, a piezoelectric crystal biosensor for determination of Candida (Candida albicans (hereinafter referred to as C. albicans)) which is a pathogenic yeast, will be described in detail as an embodiment of the piezoelectric crystal biosensor of the present invention.

FIG. 1 is a perspective view of the piezoelectric crystal biosensor. In FIG. 1, a pair of electrodes 2 on which C. albicans antibody 3 was immobilized were provided on the opposite sides of a resonator in the form of a piezoelectric crystal 1. These electrodes 2 were connected with an oscillator circuit 6 through lead wires 4 as shown in FIG. 3. An AT-cut piezoelectric crystal of 9 MHz was employed as the resonator. FIG. 2 is a sectional view of the piezoelectric crystal biosensor taken along line I--I' of FIG. 1, wherein 5 is C. albicans captured by or found to the Candida antibody. In these figures, the antibody 3 and the yeast 5 are extremely enlarged.

The C. albicans antibody was immobilized to form a receptor on the surface of the electrodes in the following manner. The surface of each electrode 2 of the piezoelectric crystal 1 was plated with palladium and thereafter the electrode 2 was electrolytically oxidized. After treating the piezoelectric crystal in 2% solution of .gamma.-aminopropyl triethoxy silane in acetone for an hour, washing the same with water and drying, the resonant frequency F.sub.1 was measured. The measurement was performed by connecting the lead wires 4 to the oscillator circuit 6 with the use of the frequency counter 7. Subsequently, the piezoelectric crystal was treated to in 5% aqueous solution of glytaraldehyde for three hours and C. albicans antibody was added dropwise on the electrodes and allowed to stand for 30 minutes to thereby immobilize the antibody on the electrodes. Then the unreacted aldehyde groups were treated with 0.1M glycine for 30 min.

The piezoelectric crystal biosensor 8 for the determination of C. albicans thus formed was operated as follows. This sensor was washed with 0.5M NaCl solution and immersed in C. albicans sample solution or liquid. After allowing the sensor to stand for 30 minutes, the sensor was washed with 0.5M NaCl solution again and the resonant frequency F.sub.2 was measured. FIG. 4 shows the relationship between the resonant frequency and the C. albicans concentration, wherein the abscissa refers to the concentration of C. albicans while the ordinate refers to the frequency change (.DELTA.F=F.sub.1 -F.sub.2). This plot is formed by measuring F.sub.2 with the use of sample liquids of various C. albicans concentrations. Each microbial concentration is measured with a hemocytometer. In FIG. 4, each mark O represents a measured value. FIG. 4 indicates that the resonant frequency or shift change, .DELTA.F, increases depending on the microbial concentration. In FIG. 4, the dotted line represents a resonant frequency change caused by the antibody alone.

FIG. 5 shows a plot of .DELTA.F relative to the microbial concentration of solutions of Saccharomyces (Saccharomyces cerevisiae (hereinafter referred to as S. cerevisiae)), which is also a yeast, measured in the same manner as the one described above with the piezoelectric crystal biosensor for C. albicans of the present invention. FIG. 5 suggests that the frequency shows no change depending on the S. cerevisiae concentration. Further examinations on Escherichia coli and Bacillus are carried out. Consequently, it is found that no change in the frequency is observed in these cases similar to the case of S. cerevisiae. Thus the piezoelectric crystal biosensor for C. albicans of the present invention has an excellent selectivity or specificity.

As a result of an examination on a mixture of C. albicans with S. cerevisiae, it is found that the change in he frequency depends on the concentration of C. albicans alone.

The inventors have succeeded in determining the concentration of biochemicals with a high accuracy by utilizing a piezoelectric crystal biosensor, wherein an antibody or an antigen is immobilized on the surface of each electrode and the biosensor is mounted in a container in the form of a flow type cell. In the piezoelectric crystal biosensor system of the present invention, the piezoelectric crystal biosensor is incorporated in a flow type cell to thereby handle the sensor in a liquid at any time. To avoid unstable oscillation or fluctuation of the resonant frequency caused by mechanical pressure, the piezoelectric crystal is immersed in water as a whole. Further, since the resonant frequency of the oscillator varies depending on the temperature, conductivity and flow rate of the liquid, the measurements of the frequency before and after the antigen-antibody reaction are carried out by replacing the sample liquid with distilled water and feeding the distilled water maintained at a given temperature in a thermostatic bath to the cell at a constant rate.

Further, the inventors have succeeded in enhancing the sensitivity of a piezoelectric crystal biosensor. After all antibody or antigen is immobilized on the surface of each electrode of the piezoelectric crystal, latexes or other fine particles, on which an antibody or an antigen is immobilized, via antigen-antibody reaction to a substrate, is bound via antigen-antibody reaction with the immobilized antibody or antigen on the piezoelectric crystal.

In the determination with the piezoelectric crystal biosensor according to the present invention, the weight change of the surface of the piezoelectric crystal is amplified with latexes or other fine particles.

The piezoelectric crystal biosensor was prepared in the following procedure. The surface of each electrode of the piezoelectric crystal was plated with palladium and anodized in 0.5M NaOH for one hour. Then it was treated in 10% .gamma.-amino propyl triethoxy silane in acetone for two hours and then in 5% glutaraldehyde aldehyde for three hours. Subsequently, it was immersed in 1 mg/ml solution of protein A for formimg a receptor to be immobilized. It was further immersed in 0.1M glycine for 30 minutes to remove unreacted aldehyde groups.

The determination in this example was performed according to a flow system as shown in FIG. 7. FIG. 6 shows a biosenor and a container or cell while FIG. 7 shows the entire system. In FIG. 6, an electrode 62 on which the receptor is immobilized in the above-mentioned procedure was provided on each side of a piezoelectric crystal 61. Each electrode is connected to a lead wire 63. A cell 64 is placed in such a manner as to accommodate therein the piezoelectric crystal 61. Pipes 65 are provided in the cell to circulate liquid therein. The lead wires 63 are drawn outside the cell 64 and connected to an oscillator circuit 66 as shown in FIG. 7. The oscillator circuit 66 is connected to a frequency counter 67 to which a computer 68 is connected to process the data obtained by the frequency counter 67. One of the pipes or outlet 65 connected to the cell 64 placed around the piezoelectric crystal 61 is connected to a pump 69 to pass or circulate the liquid through the cell 64, while the other pipe or inlet 65 is connected to an outlet of a three-way valve 70. One inlet of the three-way valve 70 is selectively switched to open for introducing into the cell 64 distilled water 72 stored in a thermostatic bath 71 and another inlet 73 is selectively switched to open for introducing 0.5M NaCl and glycine-hydrochloride buffer solution (pH 2.8) and sample solutions.

The determination of human IgG with the piezoelectric crystal biosensor system was carried out in the following manner. A glycine-hydrochloride buffer solution (pH 2.8) was circulated through the cell to remove adsorbates. Then the content of the cell was replaced by distilled water and the oscillation frequency F.sub.1 was measured while feeding the distilled water at the constant rate. The resonant frequency was monitored continuously until the frequency become constant. Then human IgG solution was circulated through the cell and allowed to react with the receptor for 30 minutes at 30.degree. C. Then a solvent liquid in the form of 0.5M NaCl was circulated therethrough to remove non-specific adsorbates or substances attached to the receptor. The content of the cell was replaced with distilled water again and the oscillation frequency F.sub.2 was measured while feeding the distilled water at a constant rate. Then another solvent liquid in the form of glycine-hydrochloride buffer solution (pH 2.8) was circulated through the cell to thereby remove the specific adsorbate for rinse.

FIG. 8 shows a relationship between the human IgG concentration and the resonant frequency change of the piezoelectric crystal biosensor on which protein A is integrated as the receptor. The ordinate refers to the resonant frequency change (.DELTA.F=F.sub.1 -F.sub.2) while the abscissa refers to human IgG concentration. Thus it is found that the frequency varies depending on human IgG concentration.

It is further found that the frequency returns to the original value after circulating the buffer solution (pH 2.8) through the cell and that the frequency further varies by an additional reaction and the sensor is used over ten times. As a result of an examination on human albumin, no response is obtained, which suggests that this system responds specifically to IgG. A similar result is obtained when the anti-human IgG antibody is employed.

Referring to the drawings, an application of the present invention to the determination of human IgG will be described in detail.

FIG. 9 shows the principle of the present arrangement, wherein numeral 91 is anti-human IgG antibody immobilized on an electrode 92 of a piezoelectric crystal, 93 is human IgG which is a sample substrate and 94 is a fine article in the form of a latex on which anti-human IgG antibody 91 is immobilized in order to enhance the sensitivity.

The piezoelectric crystal biosensor was prepared in the same procedure as the one described in Example 2 except that anti-human IgG was immobilized on the biosensor. The same determination system as that used in Example 2 was employed.

In the above structure, glycine-hydrochloride buffer solution (pH 2.8) was introduced into the cell to remove adsorbates. Then the content of the cell was replaced with liquid in the form of distilled water and the resonant frequency F.sub.1 was measured at a constant flow rate of distilled water. Subsequently, human IgG solution was introduced into the cell and allowed to react with the receptor for 30 minutes at 30.degree. C. in the cell.

0.5M NaCl was circulated through the cell to remove non-specific adsorbates. Then the resonant frequency F.sub.2 was measured again. Further latexes on which anti-human IgG antibody was immobilized were introduced into the cell and allowed to react with human IgG bound to the receptor for 30 minutes. After passing 0.5M NaCl through the cell again, the resonant frequency F.sub.3 was measured. Table 1 shows the frequency shift in response to the binding of IgG (F.sub.1 -F.sub.2) and that enhanced by the latexes (F.sub.1 -F.sub.3). Table 1 suggests that these latexes can enhance the sensitivity.

Referring to the drawings, an application of the present invention to the determination of human IgG will be described in detail.

FIG. 10 shows the principle of the present arrangement, wherein numeral 101 is protein A immobilized on the surface of an electrode 102 of a piezoelectric crystal, 103 is human IgG which is a sample substrate and 104 is a latex on which anti-human IgG antibody 105 (mouse IgG.sub.1) is immobilized in order to enhance the sensitivity.

The piezoelectric crystal biosensor was prepared in the same procedure as that described in Example 2. The same determination system as that used in Application 2 was employed.

In the above structure, glycine-hydrochloride buffer solution (pH 2.8) was introduced into the cell to remove adsorbates. Then the content of the cell was replaced with distilled water and the resonant frequency F.sub.1 was measured at a constant flow rate of distilled water. Subsequently, human IgG solution was introduced into the cell and allowed to react with the receptor for 30 minutes in the cell. 0.5M NaCl was circulated through the cell to remove non-specific adsorbates. After replacing the content of the cell with distilled water, the resonant frequency F.sub.2 was measured again. Further latexes, on which anti-human IgG antibody (mouse IgG.sub.1) was immobilized, were introduced into the cell and allowed to react with the bound IgG for 30 minutes. After introducing phosphate buffer solution (pH 6) into the cell to thereby remove latexes directly bound to protein A, the content of the cell was replaced with distilled water and the resonant frequency F.sub.3 was measured.

Comparing the obtained response upon human IgG, i.e., .DELTA.F.sub.1-2 (F.sub.1 -F.sub.2) with the one enhanced with the latexes, i.e., .DELTA.F.sub.1-3 (F.sub.1 -F.sub.3), it was found that .DELTA.F.sub.1-3 exhibited an enhanced response proportional to .DELTA.F.sub.1-2. This fact suggests that the latexes, on which anti-human IgG is immobilized, can enhance the sensitivity.

The constituents or species of particular biochemical are analyzed by the steps of immobilizing materials exhibiting different adsorptivities upon various biochemicals on the surface of a piezoelectric crystal, successively introducing eluents different in properties through the cell and determining change in the resonant frequency before and after the elution.

Namely, a sample to be analyzed is previously adsorbed on the surface of the piezoelectric crystal biosensor on which a receptor selected from enzymes, sugars, lipids, co-enzymes, amino acids and proteins such as lectins antibodies or protein A, is immobilized and then the constituents of the sample are eluted with eluents slightly different in pH value or ionic strength from each other or containing organic solvents. Thus the presence and amount of each constituent can be determined from the resonant frequency change of the piezoelectric crystal biosensor before and after the elution.

The constituents of biochemicals can be analyzed with the use of a piezoelectric crystal biosensor by taking advantage of the specificity of adsorbent with respect to materials immobilized on the surface of the piezoelectric crystal to adsorb various substances. This sensor has wide application by selecting proper materials to be immobilized on the surface and eluents.

Referring to the drawings, an application of the present invention to the analysis of mouse .gamma.-globulin will be described in detail.

FIG. 11 shows the principle of the present arrangement wherein numeral 111 is protein A immobilized on the surface of an electrode 112 of a piezoelectric crystal and 113, 114 and 115 are, respectively, mouse IgG.sub.1, IgG.sub.2a and IgG.sub.2b to be analyzed. As shown in FIg. 11(a), immobilized protein A reacted with mouse IgG and was rinsed (FIG. 11(b)). Then the resonant frequency F.sub.0 (Hz) was measured. Subsequently IgG.sub.1 113 was eluted with an eluent A and the resonant frequency F.sub.1 (Hz) was measured again. Thus the amount of IgG.sub.1 113 was determined by a change in the resonant frequency, i.e., F.sub.1 -F.sub.0. The amounts of IgG.sub.2a 114 and IgG.sub.2b 115 can be determined in the same procedure.

The piezoelectric crystal biosensor was prepared in the same procedure as that described in example 2. The determination in this example was performed according to a flow system as shown in FIG. 7.

In the system as shown in FIG. 7, a glycine-hydrochloride buffer solution (pH 2.8) was introduced into the cell to remove adsorbates. Then the content of the cell was replaced with distilled water and the resonant frequency was measured in a constant flow of distilled water. Subsequently, 0.1 mg/ml mouse .gamma.-globulin solution in phosphate buffer solution (pH 8) was introduced into the cell and allowed to react with the reaction for 30 minutes while maintaining the cell at 30.degree. C.

Then the content of the cell was replaced with distilled water and the resonant frequency was measured. Subsequently, it was successively eluted with phosphate/citrate buffer solutions of pH 7.0, 6.5, 6.0, 5.5, 5.0, 4.5, 4.0, 3.5 and 3.0 and the resonant freqency was measured followed by each elution. FIG. 12(a) shows the resonant frequency change thus measured. FIG. 12(b) is a graph which shows the difference in the resonant frequencies measured before and after each elution obtained from the result in FIG. 12(a). FIG. 12(b) suggests that there are three obvious peaks.

These peaks correspond to IgG.sub.1, IgG.sub.2a and IgG.sub.2b, respectively. This result well conforms with that obtained by affinity chromatography with the use of protein A immobilized gel column, P.L. Ey et al Immunochemistry, 15 (1978) 429.

The constituents of human IgG were analyzed in the same system and in the same manner as those described in Example 2. Namely, a piezoelectric crystal biosensor on which protein A was immobilized was used as in Example 2. Similar to Example 2, glycine hydrochloride buffer solution (pH 2.8) was introduced into the cell to thereby remove adsorbates. Then the content of the cell was replaced with distilled water and the resonant frequency was measured in a constant flow of distilled water. Subsequently, 0.1 mg/ml solution of human .gamma.-globulin in phosphate buffer solution (pH 7) was introduced into the cell and allowed to react with the receptor for 30 minutes while maintaining the cell to 30.degree. C. Then the content of the cell was replaced with distilled water and the resonant frequency was measured. Subsequently each of the human .gamma.-globulin species was successively eluted with phosphate-citrate buffer solutions of pH 6.5, 6.0, 5.5, 5.0, 4.5, 4.0, 3.5, 3.0 and 2.5 and the resonant frequency was measured after each solution. FIG. 13 is a graph of the resonant frequencies difference before and after the elution determined from a change in the resonant frequency. This result shows a similar tendency to that reported by R. C. Duhamel, P. H. Schur and K. Brendel (cf. J. Immunol. Methods, 31, 211 (1979)), i.e., showing the elution of IgG.sub.2 and IgG.sub.4 at around pH 4.7 and the elution of IgG.sub.1 and IgG.sub.4 at around pH 4.3.

In this application, protein A alone was employed as a material which can adsorb biochemicals, furthermore, two or more materials, which can adsorb the biochemicals to be analyzed, may be immobilized. In such a case, each biochemical may be analyzed by selecting appropriate eluents by taking advantage of the difference in the ability of the materials immobilized on the surface of the piezoelectric crystal to adsorb the biochemicals to be analyzed.

A plurality of biochemicals can be analyzed by an analytical system equipped with a plurality of piezoelectric crystal biosensors each having a different material immobilized or chemically treated on its surface. Further the analysis can be accelerated by measuring the referential piezoelectric crystal employing in non-stationary state and measuring the difference between the resonant frequency of referential piezoelectric crystal and the resonant frequencies of piezoelectric crystal biosensors.

Namely, the analysis can be accelerated by using an analytical system wherein piezoelectric crystals on which no material is immobilized are used as referential sensors, which can remove deviations effect of shortperiod aging and changes in the conductivity and temperature of the sample solution.

Referring to the drawings, an application of the present invention to an ABO blood type sensor will be described in detail.

FIG. 14 is a perspective view of a piezoelectric crystal biosensor and a cell. Piezoelectric crystals of AT-cut 9 MHz are employed. An electrode 142 is provided on each side of each piezoelectric crystal 141 and a lead 143 is connected thereto. A cell 144 is placed in such a manner as to accommodate therein piezoelectric crystals 141. A pipe 145 is provided in the cell 144 to thereby circulate a liquid therethrough. The leads 143 are drawn outside the cell 144. FIG. 15 is a perspective view of a piezoelectric crystal biosensor equipped with piezoelectric crystals 151 of GT-cut 4 MHz and a cell. On three piezoelectric crystals, Phaseolus Limensis Agglutinin, Bandeiraea Simplicifolia Lectin I and Ulex Europaeus Agglutinin I are immobilized, respectively.

FIG. 16 is a block diagram of the determination system for biochemicals with the use of piezoelectric crystal biosensors. A lead 163 drawn from an electrode 162 provided on the surface of a piezoelectric crystal 161 is connected to a oscillator circuit 166 which is connected to a frequency counter 167.

One end of a pipe provided in a cell disposed around the piezoelectric crystal 1 is connected to a pump 169 to thereby circulate liquid through the cell. The other end of the pipe is connected to the outlet of a solenoid valve 1610. The inlets of the solenoid valve are mounted to another solenoid valve 1611 and a sample inlet 1612. The inlets of the solenoid valve 1611 are connected to a reservoir 1613 of 0.05M phosphate buffer solution (pH 7.5) and a reservoir 1614 of 0.1M .alpha.-L-fucose and 0.1M N-acetyl-D-glucosamine. The frequency counter 167, peristalic pump 169 and solenoid valves 1610 and 1611 are connected to a computer 168 by which the determination system is controlled.

The piezoelectric crystal was prepared in the following manner. The surface of each electrode of the piezoelectric crystal was plated with palladium and treated anodically to oxidize in 0.5M NaOH for one hour.

Then it was treated in and acetone solution containing 5% trisyl chloride and 1.2% pyridine for 30 minutes and washed with 5 mM HCl. Each lectin was immobilized by immersing the piezoelectric crystal in 1 mg/ml lectin solution for one hour. It was further treated in 0.1M glycine solution for 30 minutes to thereby remove unreacted aldehyde groups.

ABO blood type judgement by this device was carried out in the following procedure.

Three piezoelectric crystals each having a lectin immobilized thereon and a referential piezoelectric crystal were previously resonated in a cell through which buffer solution was passed. Then the solenoid valve 1610 was switched to thereby introduce blood cell sample via the sample inlet 1612. The sample was arbitrarily diluted by adjusting the solenoid valve 1610. When the sample was passed through the cell, the peristalic pump 169 was controlled so as to maintain a low flow rate to thereby secure sufficient progress of the reaction. Then phosphate buffer pH 7 was passed through the cell to remove non-specific adsorbates. The resonant frequency of each piezoelectric crystal was measured. The differences of the resonant frequency between each of the piezoelectric crystals on which one of the three lectins was, respectively, immobilized and the referential piezoelectric crystal was measured. Thus the blood type was judged depending on a change in the data determined before and after the reaction with the sample.

As a result, it was found that the piezoelectric crystal on which Phaseolus Limensis Agglutinin was immobilized responded to erythrocytes having type A factor alone. On the other hand, the one on which Bandeiraea Simplicifolia Lectin I was immobilized responded to both of type A and type B factors but show higher response to the latter. Thus the blood types of A, B and AB can be distinguished from each other by comparing the responses by the pieozoelectric crystal on which Phaseolus Limensis Agglutinin was immobilized. In contrast, the piezoelectric crystal on which Ulex Europaeus Agglutinin I was immobilized responded to type O erythrochtes alone.

Then the solenoid valve 11 was switched to thereby introduce 0.1M .alpha.-L-fucose and 0.1M N-acetyl-D-glucosamine (pH 7.5) into the cell. Thus erythrocytes bound to the surface of the lectins were removed. Subsequently a sufficient amount of phosphate buffer (pH 7.5) was introduced and the determination was performed again.

As described before, the analytical device of the present invention can accelerate continuous judgement of ABO blood types. Further a smaller cell can be used in a device wherein GT-cut piezoelectric crystals are employed, which brings about an additional advantage that only a smaller amount of a sample is required.

While the inventors have shown and described particular embodiments of our invention, it will be obvious to those skilled in the art that various changes and modifications may be made without departing from our invention in its broader aspects and we, therefore, intend in the appended claims to cover all such changes and modifications as full within the true spirit and scope of our invention.