NON-RADIOACTIVE CARRIERS AND RADIOACTIVE DIAGNOSTIC AGENT

Abstract: A radioactive diagnostic agent which comprises (1) the unit of a polyformyl compound having at least three formyl groups per molecule, (2) at least two units of an amino group-containing chelating compound bonded to the poly­ formyl compound with intervention of a methyleneimine linkage (-CH=N-) or a methyleneamine linkage (-CH₂NH-) formed by the condensation between the formyl group in the polyformyl compound and the amino group in the chelating compound, optionally followed by reduction, (3) at least one unit of an amino group-containing physiologically active substance bonded to the polyformyl compound with inter­ vention of a methyleneimine linkage or a methyleneamine linkage formed by the condensation between the formyl group in the polyformyl compound and the amino group in the physiologically active substance, optionally followed by reduction, and (4) at least two radioactive metallic elements of which each is bonded to the chelating compound through a chelating bond.

Description: The present invention relates to non-radioactive carriers and a radioactive diagnostic agent. More particularly, it relates to a radioactive diagnostic agent which comprises a formyl group-containing, chelating substance comprising the unit of a polyformyl compound and the unit of an amino group-containing chelating compound in combination, and an amino group-containing physiologically active substance and a radioactive metallic element bonded to said chelating substance, and non-radioactive carriers therefor. For the purpose of a non-invading nuclear medical diagnosis such as recording, dynamic study and quantitative measurement of the blood circulation system, detection of physiological abnormality or localization of abnormality by imaging, there have been widely used physiologically active substances labeled with iodine-131 ( 131 I) such as 131 I-labeled serum albumin and ¹³¹I-labeled fibrinogen. However, 131 I has a long half life of about 8 days and emits beta-rays so that the patient administered therewith is exposed to a large quantity of radiation. In order to overcome the said drawback in the ¹³¹I-labeled physiologically active substances, attempts have been made to provide radioactive diagnostic agents comprising physiologically active substances and radioactive metallic elements having more favorable physical properties than iodine-131 combined thereto. Among such attempts, there is known a labeling method wherein a physiologically active substance is treated directly with a radioactive metal salt to make a chelate compound, which may be used as a radioactive diagnostic agent. For instance, human serum albumin is treated with an aqueous solution containing technetium-99m (⁹⁹ m Tc) in the form of pertechnetate in the presence of a reducing agent to give ⁹⁹ m Tc-labeled human serum albumin. Further, for instance, bleomycin is treated with an aqueous solution containing indium-111 (¹¹¹In) in the form of indium chloride to give ¹¹¹In-labeled bleomycin. However, the chelate forming property of those physiologically active substances is not sufficient, and the once formed chelating bond is readily broken. In fact, ⁹⁹ m Tc-labeled serum albumin and ¹¹¹In-labeled bleomycin are low in the stability after administration into living bodies so that the behavior of the radioactivity in such bodies does not coincide with that of serum albumin or bleomycin as the physiologically active substance. This is a fatal defect for the nuclear medical diagnosis based on the exact trace of the behavior of the radioactivity which should coincide with the behavior of the physiologically active substance. In recent years, attention was drawn to some chelating compounds which show on one hand a strong chelate forming property to a variety of metals and have on the other hand an amino group or a carboxyl group highly reactive to various physiologically active substances, and by utilization of these characteristic features, attempts have been made to combine a radioactive metallic element and a physiologically active substance to them. Examples of those chelating compounds are diethylenetriamine-pentaacetic acid, ethylenediamine-triacetic acid, 3-oxobutyral-bis(N-methylthiosemicarbazone)carboxylic acid, deferoxamine, 3-aminomethylene-2,4-pentanedione-bis(thiosemicarbazone) derivatives and 1-(p-aminoalkyl)phenylpropane-1,2-dione-bis(N-methylthiosemicarbazone) derivatives. [Krejcarek: Biochemical & Biophysical Research Comm, Vol. 77, 2, 581-585 (1977); Leurg: Int. J. Appl. Radiation & Isotopes, Vol. 29, 687-692 (1978): Japanese Patent Publn. (unexamined) Nos. 56-34634, 56-125317, 57-102820. Since the resulting products are stable and retain the activities of the physiologically active substances combined therein, they are suitable for the diagnostic use. However, the products combined with physiologically active substances which usually have a large molecular weight such as fibrinogen (molecular weight, about 340,000) and IgG (molecular weight, about 160,000) can hardly provide a sufficiently high radioactivity as necessitated for diagnosis. In order to overcome the above drawback, there can be considered to combine a physiologically active substance with many chelating compounds and combining the resulting chelating bonds with many radioactive metallic elements. While this method will assure a high radioactivity, the resulting physiologically active substance may be unfavorably denatured or its physiological activity may be undesirably decreased or lost. Besides, a physiologically active substance having a large molecular weight is preferred to administer to human beings at a smaller dose in view of its antigen property. For realization of such administration, the physiologically active substance is also desired to have a higher radioactivity. As a result of extensive study, it has now been found that the use of a formyl group-containing, chelating substance comprising the unit of a polyformyl compound and the unit of an amino group-containing chelating compound in combination as a carrier for a physiologically active substance and a radioactive metallic element can afford a radioactive diagnostic agent having a relatively high radioactivity per molecule without causing any deterioration or decrease of the physiological activity inherent to the physiologically active substance. According to the present invention, there is provided a non-radioactive carrier which comprises (1) the unit of a polyformyl compound having at least three formyl groups per molecule, (2) at least two units of an amino group-containing chelating compound bonded to the polyformyl compound with intervention of a methylenimine linkage (-CH=N-) or a methylenamine linkage ( -CH₂NH- ) formed by the condensation between the formyl group in the polyformyl compound and the amino group in the chelating compound, optionally followed by reduction. There is also provided a radioactive diagnostic agent which comprises (1) the unit of a polyformyl compound having at least three formyl groups per molecule, (2) at least two units of an amino group-containing chelating compound bonded to the polyformyl compound with intervention of a methylenimine linkage (-CH=N-) or a methylenamine linkage ( -CH₂NH-) ) formed by the condensation between the formyl group in the polyformyl compound and the amino group in the chelating compound, optionally followed by reduction, (3) at least one unit of an amino group-containing physiologically active substance bonded to the polyformyl compound with intervention of a methylenimine linkage or a methylenamine linkage formed by the condensation between the formyl group in the polyformyl compound and the amino group in the physiologically active substance, optionally followed by reduction, and (4) at least two radioactive metallic elements of which each is bonded to the chelating compound through a chelating bond. There is further provided a physiologically active substance-combined non-radioactive carrier comprising (1) the unit of a polyformyl compound having at least three formyl groups, (2) at least two units of an amino group-containing chelating compound bonded to the polyformyl compound with intervention of a methyleimine linkage or a methylenamine linkage formed by the condensation between the formyl group in the polyformyl compound and the amino group in the chelating compound, optionally followed by reduction, and (3) at least one unit of an amino group-containing physiologically active substance bonded to the polyformyl compound with intervention of a methylenimine linkage or a methylenamine linkage formed by the condensation between the formyl group in the polyformyl compound and the amino group in the physiologically active substance, optionally followed by reduction, and being useful for preparation of said radioactive diagnostic agent. The polyformyl compound (1) is required to have at least three formyl groups in the molecule and preferred to have a higher number of formyl groups. Among those formyl groups, at least two serve to combine with the corresponding number of the amino group-containing chelating compound (2), and at least one serves to combine with the corresponding number of the physiologically active substance (3). Specific examples of the polyformyl compound (1) are polyacrolein and polymethacrolein. Preferred is polyacrolein of the formula: wherein p is usually from 3 to 4,000, preferably from 10 to 500. Such polyacrolein may be prepared, for instance, by subjecting acrolein to Redox polymerization [Schulz et al.: Makromol. Chem., Vol. 24, page 141 (1975)]. Other specific examples are poly(dialdehydosaccharides), among which typical one is dialdehydostarch of the formula: wherein p' is usually from 2 to 1000, preferably from 10 to 500. These may be prepared, for instance, by oxidizing polysaccharides (e.g. starch, amylose, dextran, purdan) with an oxidizing agent (e.g. sodium periodate) so as to form two formyl groups in each saccharide unit. As the amino group-containing chelating compound (2), there may be used any one which shows a strong chelate forming property to a radioactive metallic element and has an amino group capable of reacting to a formyl group in the polyformyl compound (1) under a relatively mild condition. Specific examples are deferoxamine (i.e. 1-amino-6,17-dihydroxy-7,10,18,21-tetraoxo-27-(N-acetyl-hydroxylamino)-6,11,17,22-tetraazaheptaeicosane) [The Merck Index, 9th Ed., page 374 (1976)], 3-aminomethylene-2,4-pentanedione-bis-(thiosemicarbazone) derivatives of the formula: wherein R¹ and R² are each each a hydrogen atom, a C₁-C₃ alkyl group or a phenyl group [EP-A-0054920], l-(p-amino-alkyl)phenylpropane-1,2-dione-bis(thiosemicarbazone) derivatives of the formula: wherein R³ and R⁴ are each a hydrogen atom or a C₁-C₃ alkyl group and n is 0 or an integer of 1 to 3 [Australian patent 533722]. Any compound which has a metal capturing property to form a chelate and does not have any amino group but can be readily modified go as to have an amino group or an amino group-containing function is also usable as the chelating compound (2) after the modification. For instance, the one bearing a carboxyl group may be reacted with hexanediamine so that it is converted into the one bearing an aminohexylaminocarbonyl group, which can be readily condensed with a formyl group. Specific examples are diethylenetriamine-pentaacetic acid, ethylenediamine-triacetic acid, 2-oxopropionaldehyde-bis(thiosemicarbazone) derivitives of the formula: wherein R⁵, R⁶, R⁷ and R⁸ are each a hydrogen atom or a C₁-C₃ alkyl group [U.S. patent 4287362] The term "physiologically active substance" as the constituent (3) is intended to mean any substance which shows a specific accumulability at a certain organ or tissue or a certain diseased locus or exhibits a specific behavior corresponding to a certain physiological state. Tracing of the behavior of such substance in a living body can provide informations useful for diagnosis. Physiologically active substances having an amino group capable of being condensed with a formyl group under a relatively mild condition is advantageously useful in this invention. Even when an amino group is not present, however, the substance may be used as the physiologically active substance (3) after any chemical modification so as to have an amino group or an amino group-containing function. Specific examples of suitable physiologically active substances are blood proteins (e.g. human serum albumin, fibrinogen), enzymes (e.g. urokinase, streptokinase), hormones (e.g. thyroid stimulating hormone, parathyroid hormone), immune antibodies (e.g. IgG), monoclonal antibodies, antibiotics (e.g. bleomycin, kanamycin), saccharides, fatty acids and amino acids. In general, this invention is favorably applicable to physiologically active substances having a molecular weight of not less than about 100,000. The term "radioactive metallic element" as the constituent (4) is intended to mean any metallic element having radioactivity, which has physical characteristics suitable for nuclear medical diagnosis and can be readily captured with the chelate forming structure in the chelating compound (2). Specific examples of the radioactive metallic element are gallium-67 (⁶⁷Ga), gallium-68 (⁶⁸Ga), thallium-201 (²⁰¹Tl), indium-111 (¹¹¹In)and tecnethium-99m (⁹⁹ m Tc). They are normally employed in their salt form, particularly in their water-soluble salt forms. For preparation of the non-radioactive carrier of the invention, the polyformyl compound (1) and the chelating compound (2) are subjected to condensation to form a methyleneimine linkage between the formyl group in the former and the the amino group in the latter, optionally followed by reduction of the methyleneimine linkage to the methyleneamine linkage. Depending on the kinds of the reactants and the reaction conditions, the number of units of the chelating compound (2) to be introduced into the polyformyl compound (1) is varied, and generally a larger number of not less than 5 units, especially of not less than 10 units, of the chelating compound (2) per each molecule of the polyformyl compound (1) is better, but at least one formyl group in the polyformyl compound (1) should be left for combination with the physiologically active substance (3). The resulting polyformyl compound (1)-the chelating compound (2) condensation or condensation-reduction product (hereinafter referred to as "the condensation or condensation-reduction product") as the non-radioactive carrier is then condensed with the physiologically active substance (3), optionally followed by reduction so as to form a methyleneimine group or a methyleneamine group between a formyl group in the polyformyl compound (1) moiety of the former and the amino group in the latter to give the physiologically active substance-combined condensation or condensation-reduction product. The number of units of the physiologically active substance (3) to be introduced into the condensation or condensation-reduction product varies with the kinds of the reactants, and the reaction conditions, and usually a smaller number of not more than about 10 units, preferably of not more than 3 units, of the physiologically active substance (3) per each molecule of the polyformyl compound (1) is desirable. Alternatively, the physiologically active substance-combined condensation or condensation-reduction product may be prepared by first condensing the polyformyl compound (1) with the physiologically active substance (3) to form a methyleneimine linkage between a formyl group in the former and an amino group in the latter, optionally followed by reduction of the methyleneimine linkage to a methyleneamine linkage, to give the physiologically active substance-combined polyformyl compound, which is then condensed with the chelating compound (2) to form a methyleneimine linkage between a formyl group in the polyformyl compound moiety of the physiologically active substance-combined polyformyl compound and an amino group in the chelating compound (2), optionally followed by reduction of the methyleneimine linkage to a methyleneamine linkage, whereby the physiologically active substance-combined condensation or condensation-reduction product is obtained. As to the numbers of the units of the chelating compound (2) and of the physiologically active substance (3), the same attention as stated above may be taken. In the above preparation procedures, the reduction to be carried out optionally after the condensation may be accomplished in a single step at the final stage. Further, each of the reactions such as condensation and reduction may be carried out by per se conventional procedures. Furthermore, in the reduction, a formyl group may be converted into a hydroxymethyl group simultaneously with the conversion of a methyleneimine linkage into a methyleneamine linkage. Usually, the condensation can proceed easily at room temperature. For the reduction, a reductive metal hydride compound such as sodium borohydride is favorably employed as the reducing agent. At any stage in the above preparation procedures, the reaction product may be optionally purified by per se conventional methods such as column chromatography, gel permeation and dialysis. The thus obtained physiologically active substance-combined condensation or condensation-reduction product may be then labeled with the radioactive metallic element (4) to give a radioactive metallic element-labeled, physiologically active substance-combined condensation or condensation-reduction product, which is a radioactive diagnostic agent of the invention. Depending upon the kind or state of the radioactive metallic element (4), two different labeling procedures may be adopted. When the radioactive metallic element (4) is in a valency state which can form a stable chelate compound, the physiologically active substance-combined condensation or condensation-reduction product may be contacted with the radioactive metallic element (4) in an aqueous medium to form the radioactive metallic element-labeled, physiologically active substance-combined condensation or condensation-reduction product as a radioactive diagnostic agent. This labeling manner may be applied to ⁶⁷Ga or ¹¹¹In. When the radioactive metallic element (4) is in a valency state which has to be changed for the formation of a stable chelate compound, the physiologically active substance-combined condensation or condensation-reduction product may be contacted with the radioactive metallic element (4) in an aqueous medium in the presence of a reducing agent or an oxidizing agent to form the radioactive metallic element-labeled, physiologically active substance-combined condensation or condensation-reduction product. This labeling manner may be applied to ⁹⁹ m Tc. Examples of the reducing agent are stannous salts, i.e. salts of divalent tin ion (Sn ++ ). Specific examples are stannous halides (e.g. stannous chloride, stannous fluoride), stannous sulfate, stannous nitrate, stannous acetate and stannous citrate. Sn ++ ion-bearing resins, e.g. ion-exchange resins charged with Sn ++ ion, are also suitable. When, for example, the radioactive metallic element (4) is ⁹⁹ m Tc, the physiologically active substance-combined condensation or condensation-reduction product may be treated with ⁹⁹ m Tc in the form of a pertechnetate in an aqueous medium in the presence of a reducing agent, e.g. a stannous salt. There is no particular requirement concerning the order of the introduction of the above reagents into the reaction system. Usually, however, initial mixing of the stannous salt with the pertechnetate in an aqueous medium should be avoided. The stannous salt may be used in an amount that can sufficiently reduce the pertechnetate. The radioactive diagnostic agent should have sufficient radioactivity and radioactivity concentration to assure reliable diagnosis. For instance, the radioactive metallic element ⁹⁹ m Tc may be used in an amount of 0.1 to 50 mCi in about 0.5 to 5.0 ml at the time of administration. The amount of the physiologically active substance-combined condensation or condensation-reduction product should be sufficient to form a stable chelate compound with the radioactive metallic element (4). The thus produced radioactive metallic element-labeled, physiologically active substance-combined condensation or condensation-reduction product as a radioactive diagnostic agent is sufficiently stable, and therefore it may be stored as such and supplied on demand. When desired, the radioactive diagnostic agent may contain any suitable additive such as a pH controlling agent (e.g. an acid, a base, a buffer), a stabilizer (e.g. ascorbic acid) or an isotonizing agent (e.g. sodium chloride). The radioactive metallic element-labeled, physiologically active substance-combined condensation or condensation-reduction product of this invention is useful for nuclear medical diagnosis. For example, the ⁹⁹ m Tc or ⁶⁷Ga-labeled streptokinase-combined condensation or condensation-reduction product may be used for recording and functional measurement of myocardium. Also, for example, the ⁹⁹ m Tc-labeled, human serum albumin-combined condensation or condensation-reduction product can be used for recording, dynamic study and quantitative measurement of the blood circulation system by intravenous administration to the human body. Further, for example, the ⁹⁹ m Tc-labeled, fibrinogen or urokinase-combined condensation or condensation-reduction product may be used for detection and recording of thrombosis as well an the localization of thrombosis, since they accumulate at the locus of thrombosis. Furthermore, for example, the ⁹⁹ m Tc-labeled, streptokinase-combined condensation or condensation-reduction product is useful for determination of the locus of a myocardial infarction. Moreover, the ⁹⁹ m Tc-labeled, thyroid stimulating hormone-combined condensation or condensation-reduction product is useful for the detection and recording of a cancer at the thyroid gland. The radioactive diagnostic agent of this invention may be administered to a patient in an amount sufficient to produce the radioactivity necessary for examination of a particular organ or tissue, by any appropriate route, usually through an intravenous route. For instance, the intravenous administration of a ⁹⁹ m Tc-labeled radioactive diagnostic agent in an amount of 1 to 3 ml by volume having a radioactivity of 1 to 20 mCi to a patient is quite suitable for diagnostic purpose. The advantages of the physiologically active substance-combined condensation or condensation-reduction product of this invention, i.e. the physiologically active substance-combined non-radioactive carrier may be summarized as follows: (a) it is stable over a long period of time after manufacture; (b) since it can be produced under mild conditions, no unfavorable side reactions such as inactivation, denaturation or decomposition are caused in the physiologically active substance; (c) any physiologically active substance having an amino group can be used as the starting material; (d) even when an amino group is not present, the introduction of such group into a physiologically active substance makes it usable as the starting material; (e) a radioactive metallic element-labeled, physiologically active condensation or condensation-reduction product can be formed by a very simple procedure, e.g. by merely contacting the physiologically active substance-combined condensation or condensation-reduction product with a radioactive metallic element in an aqueous medium. The advantages of the radioactive metallic element-labeled, physiologically active substance-combined condensation or condensation-reduction product used as a radioactive diagnostic agent may be also summaried as follows: (a) it is stable over a long period of time after manufacture; (b) the labeling efficiency with the radioactive metallic element is extremely high (nearly 100 %); (c) since the labeling operation is quite simple, no unfavorable side reactions such as inactivation, denaturation or decomposition are caused in the physiologically active substance bonded to the condensation or condensation-reduction product; (d) among various radioactive metallic elements, the most suitable one for the diagnostic purpose may be chosen so that the diagnosis can be improved not only in quantity but also in quality with reduction of the exposure dose. Practical and presently preferred embodiments of the invention are iilustratively shown in the following Examples. Reference Example 1 Preparation of polyacrolein:- Water (50 ml) was charged in a flask and heated under reflux while introducing nitrogen gas therein. After cooling below 20°C, potassium peroxodisulfate (0.475 g) and acrolein (purity, more than 95 %) (10 ml) were added thereto. After acrolein was dissolved, a solution of silver nitrate (0.296 g) in water (6 ml) was dropwise added thereto in about 1 minute while vigorous agitation. The reaction was continued for 2.5 hours, during which care was taken to avoid the elevation of the temperature above 20°c. After the reaction was completed, the reaction mixture was added to water (50 ml), whereby the produced polyacrolein was precipitated. The precipitate was collected by filtration, washed with water two times and dispersed in a solution of sodium thiosulfate (0.5 g) in water (50 ml), followed by stirring for 1 hour The dispersion was filtered to collect the solid material, which was washed with water several times and dried under reduced pressure overnight to obtain polyacrolein. Polyacrolein (50 mg) as prepared above was dissolved in dimethylsulfoxide (10 ml), sodium borohydride (3 mg) was added thereto, and stirring was continued at room temperature for 1 hour. To the resulting mixture, ethyl acetate (10 ml) was added to precipitate partially reduced polyacrolein. The precipitate was collected by filtration, dissolved in water and subjected to measurement of molecular weight by high speed liquid chromatography under the following conditions: Column: TSK-3000SW Solvent: 0.05M Tris-0.15M sodium chloride-hydrochloric acid buffer (pH, 7.4) Flow rate: 1.0 ml/min Since the partially reduced polyacrolein was eluted at a retention volume of 23.2 ml, the molecular weight of polyacrolein was determined to be about 21,000. Reference Example 2 Preparation of dialdehydrodextran:- To a solution of dextran (average molecular weight, 10,000) (3.24 g) in 0.1M sodium acetate solution (pH, 4.2; 200 ml), 0.1M sodium periodate solution (40 ml) was added, and the resultant mixture was stirred at a dark place overnight. The reaction mixture was admitted in a cellulose tube and dialyzed to water for 2 days, followed by lyophilization to obtain dialdehydodextran About 50 mg of the above prepared dialdehydodextran was weighed precisely and dissolved in 0.01M phosphoric acid-0.15M sodium chloride buffer (100 ml). The resulting solution (about 5 ml) was precisely measured, 1/100 N iodine solution (5 ml) was added thereto, and further 0.15M sodium carbonate solution (1 ml) was added thereto, followed by allowing to stand at room temperature for 1.5 hours. After addition of 0.2 N sulfuric acid (2 ml), titration was carried out with 1/100 N sodium thiosulfate solution until a colorless, transparent solution was obtained. This titration value was taken as A. In the same manner as above, 0.01M phosphoric acid-0.15M sodium chloride buffer (5 ml) was titrated with 1/100 N sodium thiosulfate solution, and the resulting titration value was taken as B. The content of aldehyde groups in 1 mg of the product was calculated according to the following equation: Aldehyde groups (µmole/mg) = (A-B)x10/2W wherein W is the amount of dialdehydrodextran (mg) contained in 5 ml of the sample. As the result, the aldehyde group content in the dialdehydrodextran as prepared above was determined to be 5.1 µmole/mg. Example 1 (A) Preparation of the polyacrolein-deferoxamine condensation-reduction product as a non-radioactive carrier:- Polyacrolein (molecular weight, 21,000) (500 mg) was dissolved in dimethylsulfoxide (10 ml), and the resultant solution was admixed with a solution of deferoxamine (420 mg) in dimethylsulfoxide (10 ml). The reaction was continued at room temperature for 3 hours. To the reaction mixture, sodium borohydride (100 mg) was added, and stirring was continued at room temperature for 1 hour. The resultant mixture was subjected to dialysis to water over-night, followed by gel chromatography under the following conditions: Carrier: Sephadex® G-50 Solvent: Water Column: diameter, 4.5 cm; height, 50 cm Flow rate: 2.5 ml/min The polyacrolein-deferoxamine condensation-reduction product was eluted at a volume of 270 - 400 ml, while the unreacted deferoxamine was eluted at a volume of 550 to 600 ml. The eluate containing the polyacrolein-deferoxamine condensation-reduction product was subjected to lyophilization. The polyacrolein-deferoxamine condensation-reduction product thus obtained was dissolved in water, ferric chloride was added thereto, and the resultant solution was analyzed by high speed liquid chromatography under the following conditions to determine a retention volume of 21.2 ml: Column: TSK-3000SW Solvent: 0.05M Tris-0.15M sodium chloride-hydrochloric acid buffer (pH, 7.4) Flow rate: 1.0 ml/min Absorptive wavelength : 420 nm No free deferoxamine was detected. (The retention volume of deferoxamine in the above system is 32.8 ml.) A definite amount the polyacrolein-deferoxamine condensation-reduction product as obtained above was dissolved in water, and a sufficient amount of an aqueous ferric chloride solution was added thereto to make a 1 : 1 complex between the deferoxamine moiety in said condensation-reduction product and Fe(III) in said ferric chloride. The reaction mixture was allowed to stand for 1 hour and then subjected to measurement of absorbance at 420 nm, whereby the number of the deferoxamine moieties in said condensation-reduction product was confirmed to be 18.3 per one molecule of polyacrolein. The average molecular weight of said condensation-reduction product was thus calculated to be about 32,000. Still, deferoxamine and Fe(III) can form a 1 : 1 complex having a maximum absorption at 420 nm, and the ε max value of the complex at 420 nm is 2.63 x 10³. Example 2 (A) Preparation of the polyacrolein-hexane-diamine:3-oxobutyral-bis(N-methylthiosemicarbazone)-carboxylic acid condensate condensation-reduction product as a non-radioactive carrier:- A solution of 3-oxobutyralbis(N-methylthiosemicarbazone)carboxylic acid (hereinafter referred to as "KTS") (132 mg) in dry dioxane (5 ml) was cooled to about 10°C. Tri-n-butylamine (0.12 ml) and isobutyl chloroformate (64 µl) were added thereto. The resultant mixture was stirred at the same temperature as above for about 50 minutes to obtain a mixed acid anhydride solution. To this solution, a solution of N-tert-butyloxycarbonyl-1,6-hexanediamine (104 mg) in dry dioxane (2 ml) was added, and the resultant mixture was stirred at 10°C for about 15 hours to produce N-tert-butyloxycarbonyl-1,6-hexanediamine:KTS condensate. A few drops of conc. hydrochloric acid were added thereto to make a pH of about 2, whereby the N-tert-butyloxycarbonyl group was eliminated to give a solution of hexanediamine-KTS condensate. The above solution was added to a solution of polyacrolein (200 mg) in dimethylsulfoxide (5 ml), sodium borohydride (17.2 mg) was added thereto, and the resultant mixture was reacted at room temperature for 3 hours. The reaction mixture was subjected to dialysis by a conventional procedure for 30 hours to eliminate the unreacted reagents and lyophilized to obtain the polyacrolein-hexanediamine:KTS condensate condensation-reduction product useful as a non-radioactive carrier. The polyacrolein-hexanediamine:KTS condensate condensation-reduction product as above obtained was dissolved in water to make a concentration of 3 mg/ml, and the resulting solution was subjected to measurement of absorbance at 334 nm using water as the control, whereby the number of the KTS moieties in said condensation-reduction product was confirmed to be 21.3 per one molecule of polyacrolein. The average molecular weight of said condensation-reduction product was thus calculated to be about 29,600. Still, the hexanediamine:KTS condensate had a maximum absorption at 334 nm, and its ε max value was 4.37 x 10⁴. (B) Preparation of the fibrinogen-combined polyacrolein-hexanediamine:KTS condensate condensation-reduction product (a fibrinogen-combined non-radioactive carrier):- A solution of the non-radioactive carrier as obtained in (A) (before lyophilization) (5 ml) was added to a solution of human fibrinogen (250 mg) in 0.01M phosphate buffer-0.15M aqueous sodium chloride mixture (pH, 8.4) (50 ml), followed by stirring at room temperature for about 3 hours. Sodium borohydride (12.9 mg) was added thereto. The resultant mixture was stirred for about 1 hour. The reaction mixture was dialyzed to 0.01M glucose-0.35M sodium citrate solution at 0 to 4°C for 24 hours and then passed through a column of Sepharose 4B (diameter, 4.4 cm; height, 50 cm) using 0.01M glucose-0.35M sodium citrate solution as an eluting solvent. The eluate was lyophilized to give the polyacrolein-hexanediamine:KTS condensate condensation-reduction product as cotton-like crystals. The cotton-like crystals (100 mg) were dissolved in deoxygenated water (160 ml), and 1 mM stannous chloride solution (10 ml) and sodium ascorbate (0.6 g) were added thereto to make a clear solution. The solution was passed through a filter having a pore diameter of 0.45 µm, and the filtrate (1.5 ml) was filled in a vial flushed with nitrogen gas to obtain a fibrinogen-combined non-radioactive carrier. The above operations were effected under a sterile condition. The fibrinogen-combined non-radioactive carrier as above obtained was a pale yellow, clear solution. (C) Preparation of the ⁹⁹ m Tc-labeled, fibrinogen-combined polyacrolein-hexanediamine:KTS condensate condensation-reduction product as a radioactive diagnostic agent:- To the fibrinogen-combined non-radioactive carrier (1.5 ml) as obtained in (B), a physiological saline solution (1.5 ml) containing ⁹⁹ m Tc (3.3 mCi) in the form of sodium pertechnetate was added to obtain the ⁹⁹ m Tc-labeled, figrinogen-combined polyacrolein-hexanediamine:KTS condensate condensation-reduction product useful as a radioactive diagnostic agent. This solution was pale yellow, transparent. (D) Properties of the radioactive diagnostic agent as obtained in (C):- The radioactive diagnostic agent as obtained in (C) was subjected to electrophoresis (1.7 mA/cm; 15 minutes) using Veronal buffer (pH, 8.6) as a developing solvent and a cellulose acetate membrane as an electrophoretic membrane, and scanning was carried out by the use of a radiochromato-scanner. The radioactivity was recognized as a single peak at the locus of 0.5 cm distant from the original line towards the negative side. This locus was the same as that of the coloring band of fibrinogen with Ponceau 3R. From the above result, it may be said that the radioactive diagnostic agent has a labeling efficiency of nearly 100 % and its electric charge is substantially the same as that of fibrinogen. To the radioactive diagnostic agent as obtained in (C), 0.1M sodium diethylbarbiturate hydrochloride buffer (pH, 7.3) containing 0.05 % calcium chloride was added to make a fibrinogen concentration of 1 mg/ml. Thrombin (100 units/ml; 0.1 ml) was added thereto. The resultant mixture was allowed to stand in an ice bath for 30 minutes. The produced fibrinogen clots were completely separated from the liquor, and radioactivity was measured on the clots and also on the liquor. From the obtained results, it was detemined that the clottability of the radioactive diagnostic agent is 93 % based on the starting fibrinogen. Example 3 (A) Preparation of the polyacrolein-deferoxamine condensation product as a non-radioctive carrier:- To a solution of polyacrolein (125 mg) in dimethylsulfoxide (2.5 ml), a solution of deferoxamine (105 mg) in dimethylsulfoxide (2.5 ml) was added, and the resultant mixture was agitated at room temperature for 3 hours to produce a solution containing the polyacrolein-deferoxamine condensation product, which is useful as a non-radioactive carrier. (B) Preparation of the fibrinogen-combined, polyacrolein-deferoxamine condensation product (a fibrinogen-combined non-radioactive carrier):- The non-radioactive carrier (5 ml) as obtained above was added to a solution of human fibrinogen (200 mg) in 0.01M phosphate buffer-0.15M aqueous sodium chloride mixture (pH, 8.4) at 0 to 4°C, followed by stirring at the same temperature as above for about 3 hours. The reaction mixture was dialyzed to 0.01M glucose-0.35M sodium citrate solution at 0 to 4°C for 24 hours and then passed through a column of Sepharose 4B (diameter, 4.4 cm; height, 50 cm) using 0.01M glucose-0.35M sodium citrate solution as an eluting solvent. The eluate containing the fibrinogen-combined polyacrolein-deferoxamine condensation product was diluted with 0.01M glucose-0.35M sodium citrate solution to make a fibrinogen concentration of 1 mg/ml, and sodium ascorbate was added thereto to make a concentration of 30 mM. The resultant solution (3 ml) was admitted into a vial, followed by lyophilization to obtain a fibrinogen-combined non-radioactive carrier as a cotton-like product. The above operations were effected under a sterile condition. Example 4 (A) Preparation of the polyacrolein-deferoxamine condensation product (a non-radioctive carrier):- To a solution of polyacrolein (125 mg) in dimethylsulfoxide (2.5 ml), a solution of deferoxamine (105 mg) in dimethylsulfoxide (2.5 ml) was added, and the resultant mixture was agitated at room temperature for 3 hours to obtain a solution containing the polyacrolein-deferoxamine condensation product useful as a non-radioactive carrier. (B) Preparation of the fibrinogen-combined polyacrolein-deferoxamine condensation-reduction product (a fibrinogen-combined non-radioactive carrier):- The non-radioactive carrier (5 ml) as obtained above was added to a solution of human fibrinogen (200 mg) in 0.01M phosphate buffer-0.15M aqueous sodium chloride mixture (pH, 8.4) at 0 to 4°C, followed by stirring at the same temperature as above for about 3 hours. To the resulting mixture, sodium borohydride (7.0 mg) was added, and stirring was continued at 0 to 4°C for about 1 hour. To a portion of the reaction mixture, a solution containing ⁶⁷Ga (1 mCi) in the form of gallium chloride was added for labeling, and the resultant solution was subjected to high speed liquid chromatography under the following conditions: Column: TSK-3000SW Solvent: 0.05M Tris-0.15M sodium chloride-hydrochloric acid buffer (pH 7.4) Pressure: 100 kg/cm² Flow rate: 1.0 mL/min Detection was made on the radioactivity of ⁶⁷Ga. As the result, the eluted pattern gave three peaks attributable to ⁶⁷Ga-labeled fibrinogen, ⁶⁷Ga-labeled polyacrolein-deferoxamine condensation-reduction product and ⁶⁷Ga-labeled deferoxamine. From the area ratio of the peak due to ⁶⁷Ga-labeled polyacrolein-deferoxamine condensation-reduction product and the peak due to ⁶⁷Ga-labeled deferoxamine, 18.9 of the deferoxamine moieties were confirmed to combine to one molecule of polyacrolein. Since the number of the deferoxamine moieties in the fibrinogen-combined polyacrolein-deferoxamine condensation-reduction product was confirmed to be 14.8 per one molecule of fibrinogen, the number of fibrinogen bonded to one molecule of polyacrolein was calculated to be 0.8. The remainder of the reaction mixture was dialyzed to 0.01M glucose-0.35M sodium cintrate solution at 0 to 4°C for 24 hours and then passed through a column of Sepharose® 4B (diameter, 4.4 cm; height, 50 cm) using 0.04M glucose - 0.35M sodium citrate solution as an eluting solvent. The eluate containing the fibrinogen-combined polyacrolein-deferoxamine condensation-reduction product was diluted with 0.01M glucose-0.35M sodium citrate solution to make a fibrinogen concentration of 1 mg/ml, and sodium ascorbate was added thereto to make a concentration of 30 mM. The resultant solution (3 ml) was admitted into a vial, followed by lyophilization to obtain a fibrinogen-combined non-radioactive carrier as a cotton-like product. The above operations were effected under a sterile condition. The fibrinogen-combined non-radioactive carrier as obtained above was dissolved in sterile water to make a fibrinogen concentration of 1 mg/ml, and a sufficient amount of an aqueous ferric chloride solution was added thereto to make a 1 : 1 complex between the deferoxamine moiety in said non-radioactive carrier and Fe(III) in said ferric chloride solution. The reaction mixture was allowed to stand for 1 hour and then subjected to measurement of absorbance at 420 nm using a solution of said non-radioactive carrier in sterile water as the control, whereby the number of the deferoxamine moieties in said non-radioactive carrier was confirmed to be 14.8 per one molecule of fibrinogen. (C) Preparation of the ⁶⁷Ga-labeled, fibrinogen-combined polyacrolein-deferoxamine condensation-reduction product as a radioactive diagnostic agent:- To the fibrinogen-combined non-radioactive carrier as obtained in (B), an aqueous solution (2 ml] containing ⁶⁷Ga (2 mCi) in the form of gallium citrate was added to obtain the ⁶⁷Ga-labeled, fibrinogen-combined polyacrolein-deferoxamine condensation-reduction product as a readioactive diagnostic agent. This solution was pale yellow, transparent and had a pH of about 7.8. (C') Preparation of the ⁶⁷Ga-labeled, fibrinogen-combined polyacrolein-deferoxamine condensation-reduction product as a radioactive diagnostic agent:- The fibrinogen-labeled non-radioactive carrier obtained in (B) was dissolved in sterile water, and human fibrinogen (0.5, 0.75, 1.0, 1.5, 2.0 or 3.0 mg) dissolved in 0.01M phosphate buffer-0.15M aqueous sodium chloride mixture (pH, 8.4) and 1 ml of an aqueous solution containing ⁶⁷Ga (1 mCi) in the form of gallium citrate were added thereto. The resulting mixture was allowed to stand at room temperature for 1 hour and then subjected to measurement of lebeling rate. In the same manner as above, the labeling rate of ⁶⁷Ga-labeled, fibrinogen-combined deferoxamine as prepared by labeling ⁶⁷Ga onto fibrinogen-combined deferoxamine was also measured. The results are shown in Table 1. As understood from the above, the non-radioactive carrier of the invention could be labeled with 97.8 % of ⁶⁷Ga (1 mci) within 1 hour when 1 mg of fibrinogen was used. The conventional non-radioactive carrier (i.e. fibrinogen-combined deferoxamine) could be labeled only with 17.0 % of ⁶⁷Ga under the same condition as above. Even when 25.1 mg of fibrinogen were used, the conventional non-radioactive carrier was labeled with 83.5 % of ⁶⁷Ga at the most. It is thus appreciated that the non-radioactive carrier of the invention can afford a radioactive diagnostic agent having a higher relative radioactivity. Further, the radioactive diagnostic agent is useful in nuclear medical diagnosis aiming at detection of thrombosis. (D) properties of the radioactive diagnostic agent as obtained in (C):- The radioactive diagnostic agent as obtained in (C) was subjected to electrophoresis (1.7 mA/cm; 15 minutes) using Veronal buffer (pH, 8.6) as a developing solvent and a cellulose acetate membrane as an electrophoretic membrane, and scanning was carried out by the use of a radiochromato-scanner. The radioactivity was recognized as a single peak at the locus of 0.5 cm distant from the original line towards the negative side. This locus was the same as that of the coloring band of fibrinogen with Ponceau 3R. From the above result, it may be said that the radioactive diagnostic agent has a labeling efficiency of nearly 100 % and its electric charge is substantially the same as that of fibrinogen. To the radioactive diagnostic agent as obtained in (C), 0.1M sodium diethylbarbiturate hydrochloride buffer (pH, 7.3) containing 0.05 % calcium chloride was added to make a fibrinogen concentration of 1 mg/ml. Thrombin (100 units/ml; 0.1 ml) was added thereto. The resultant mixture was allowed to stand in an ice bath for 30 minutes. The produced fibrinogen clots were completely separated from the liquor, and radioactivity was measured on the clots and also on the liquor. From the obtained results, it was determined that the clottability of the radioactive diagnostic agent is 86 % based on the starting fibrinogen. (E) Behaviors of the radioactive diagnostic agent as obtained in (C) in rate:- The radioactive diagnostic agent as obtained in (C) (0.2 ml) was administered intravenously to each of female rats of SD strain, and the variations of the blood level and the organ distribution with the lapse of time were recorded. The results are shown in Table 2. The extremely high blood level over a long period of time and the figure of distribution into various organs of the radioactive diagnostic agent as shown in Table 2 are quite similar to those of ¹³¹I-labeled fibrinogen as conventionally employed. (F) Behaviors of the radioactive diagnostic agent as obtained in (C) in thrombosed rabbits:- Thrombosis was produced in rabbits at the femoral part by the formalin application procedure. To the rabbits, the radioactive diagnostic agent (0.5 ml) as obtained in (C) was administered through the ear vein. After 24 hours from the administration, a constant amount of the blood was sampled, and the locus of thrombosis was taken out. Radioactivity was measured on the blood and the locus of thrombosis. The radioacitivity ratio of the locus of thrombosis to the blood for the same weight was 7.44 ± 3.41 (average in 10 animals ± S.D. value). From the above results, it is understood that the radioactive diagnostic agent as obtained in (C) has the nearly same physiological activity as fibrinogen does. Thus, the radioactive diagnostic agent is useful for nuclear medical diagnosis. (G) Toxicity of the radioactive diagnostic agent as obtained in (C):- The radioactive diagnostic agent as obtained in (C) was subjected to attenuation of the radioactivity to an appropriate extent, and the resultant product was administered intravenously to groups of male and female rats of SD strain, each group consisting of five animals, at a dose of 1 ml per 100 grams of the bodyweight (corresponding to 600 times the expected dose to human beings) and also to groups of male and female mice of ICR strain, each group consisting of five animals, at a dose of 0.5 ml per 10.0 gram of the bodyweight (corresponding to 3,000 times the expected dose to human beings). As the control, the same volume of a physiological saline solution as above was intravenously administered to the separate groups of the same animals as above. The animals were fertilized for 10 days, and the variation in bodyweight during that period was recorded. No significant difference was recognized between the medicated groups and the control groups. After 10 days from the administration, all the animals were sacrificed and subjected to observation of the abnormality in various organs. No abnormality was seen in any of the animals. From the above results, it may be said that the toxicity of the non-radioactive carrier of the invention is extremely low. Example 5 (A) Preparation of the dialdehydostarch-deferoxamine condensation product as a non-radioactive carrier:- Dialdehydostarch (average molecular weight, 7000; oxidation rate, 80 %) (1 g) was dissolved in water (40 ml). Separately, deferoxamine (2.4 g) was dissolved in water (30 ml), an equimolar amount of triethylamine (388 mg) was added thereto, and the resultant solution was stirred at room temperature for 10 minutes. Both solutions were combined together and stirred at room temperature for 15 minutes. The reaction mixture was subjected to gel chromatography under the following conditions: Carrier: Sephadex®G-50 Solvent: Water Column: diameter, 4.5 cm; height, 50 cm Flow rate: 2.5 ml/min The dialdehydostarch-deferoxamine condensation product was eluted at a volume of 270 - 430 ml, while the unreacted deferoxamine was eluted at a volume of 550 to 600 ml. The eluate containing the dialdehydostarch-deferoxamine condensation product was subjected to lyophilization. The dialdehydostarch-deferoxamine condensation product thus obtained was subjected to analysis by high speed liquid chromatography under the following conditions: Column: TSK-3000SW Solvent: 0.05M Tris-0.15M sodium chloride-hydrochloric acid buffer (pH, 7.4) Pressure: 100 kg/cm² Flow rate: 1.0 ml/min Absorptive wavelength: 280 nm No free deferoxamine was detected. (The retention volume of deferoxamine in the above system is 32.8 ml.) Example 6 (A) Preparation of the dialdehydostarch-deferoxamine condensation-reduction product as a non-radioactive carrier:- Dialdehydostarch (average molecular weight, 7000; oxidation rate, 80 %) (1 g) was dissolved in water (40 ml). Separately, deferoxamine (2.4 g) was dissolved in water (30 ml), an equimolar amount of triethylamine (388 mg) was added thereto, and the resultant solution was stirred at room temperature for 10 minutes. Both solutions were combined together and stirred at room temperature for 15 minutes. Sodium borohydride (167 mg) was added thereto, and stirring was continued at room temperature for about 1 hour. The reaction mixture was subjected to gel chromatography under the following conditions: Carrier: Sephadex®G-50 Solvent: Water Column: diameter, 4.5 cm; height, 50 cm Flow rate: 2.5 ml/min The dialdehydostarch-deferoxamine condensation-reduction product was eluted at a volume of 300 - 450 ml, while the unreacted deferoxamine was eluted at a volume of 550 to 600 ml. The eluate containing the dialdehydostarch-deferoxamine condensation-reduction product was subjected to lyophilization. The dialdehydostarch-deferoxamine condensation reduction product thus obtained was subjected to analysis by high speed liquid chromatography under the following conditions: Column: TSK-3000SW Solvent: 0.05M Tris-0.15M sodium chloride-hydrochloric acid buffer (pH, 7.4) Pressure: 100 kg/cm² Flow rate: 1.0 ml/min Absorptive wavelength: 280 nm No free deferoxamine was detected. (The retention volume of deferoxamine in the above system is 32.8 ml.) A definite amount the dialdehydostarch-deferoxamine condensation-reduction product was dissolved in water, and a sufficient amount of an aqueous ferric chloride solution was added thereto to make a 1 : 1 complex between the deferoxamine moiety in said condensation-reduction product and Fe(III) in said ferric chloride solution. The reaction mixture was allowed to stand for 1 hour and then subjected to measurement of absorbance at 420 nm, whereby it was confirmed that the number of the deferoxamine moieties in said condensation-reduction product is 19.6 per molecule of dialdehydostarch. The number average molecular weight of said condensation-reduction product was thus calculated to be about 18,000. Still, deferoxamine and Fe(III) can form a 1 : 1 complex having a maximum absorption at 420 nm, and the ε max value of the complex at 420 nm is 2.63 x 10³. Example 7 (A) preparation of the dialdehydostarch-hexane-diamine:KTS condendate condensation-reduction product as a non-radioactive carrier:- A solution of KTS (132 mg) in dry dioxane (5 ml) was cooled to about 10°C. Tri-n-butylamine (0.12 ml) and isobutyl chloroformate (64 ml) were added thereto. The resultant mixture was stirred at the same temperature as above for about 50 minutes to obtain a mixed acid anhydride solution. To this solution, a solution of N-tert-butyloxycarbonyl-1,6-hexanediamine (104 mg) in dry dioxane (2 ml) was added, and the resultant mixture was stirred at 10°C for about 15 hours to produce N-tert-butyloxycarbonyl-1,6-hexanediamine:KTS condensate. A few drops of conc. hydrochloric acid were added thereto to make a pH of about 2, whereby the N-tert-butyloxycarbonyl group was eliminated to give a solution of hexanediamine-KTS condensate. The above solution was added to a solution of dialdehydostarch (200 mg) in dimethylsulfoxide (5 ml), sodium borohydride (17.2 mg) was added thereto, and the resultant mixture was reacted at room temperature for 3 hours. The reaction mixture was subjected to dialysis by a conventional procedure for 30 hours to eliminate the unreacted reagents and lyophilized to obtain dialdehydo-starch-hexanediamine:KTS condensate condensation-reduction product. The dialdehydrostarch-hexanediamine:KTS condensate condensation-reduction product as obtained above was dissolved in water to make a concentration of 3 mg/ml, and the resulting solution was subjected to measurement of absorbance at 334 nm using water as the control, whereby it was confirmed that the number of the KTS moieties in said condensation-reduction product is 11.2 per one molecule of dialdehydostarch. The average molecular weight of said condensation-reduction product was thus calculated to be about 11,500. Still, the hexanediamine:KTS condensate had a maximum absorption at 334 nm, and its ε max value was 4.37 x 10⁴. (B) Preparation of the fibrinogen-combined dialdehydostarch-hexanediamine:KTS condensate condensation-reduction product (a fibrinogen-combined non-radioactive carrier):- The hexanediamine:KTS condensate solution as obtained in (A) was added to a solution of dialdehydostarch (200 mg) in dimethylsulfoxide (5 ml), and the resultant mixture was stirred at room temperature for about 3 hours. The resulting solution containing the dialdehydrostarch-hexanediamine:KTS condensate condensation product (5 ml) was added to a solution of fibrinogen (250 mg) in 0.01M phosphate buffer-0.15M aqueous sodium chloride mixture (pH, 8.4) (50 ml), followed by stirring at room temperature for about 3 hours. Sodium borohydride (12.9 mg) was added thereto. The resultant mixture was stirred for about 1 hour. The reaction mixture was dialyzed to 0.01M glucose-0.35M sodium citrate solution at 0 to 4°C for 24 hours and then passed through a column of Sepharose® 4B (diameter, 4.4 cm; height, 50 cm) using 0.01M glucose-0.35M sodium citrate solution as an eluting solvent. The eluate was lyophilized to give the dialdehydostarch-hexanediamine:KTS condensate condensation reduction product as cotton-like crystals. The cotton-like crystals (100 mg) were dissolved in deoxygenated water (160 ml), and 1 mM stannous chloride solution (10 ml) and sodium ascorbate (0.6 g) were added thereto to make a clear solution. The solution was passed through a filter having a pore diameter of 0.22 µm, and the filtrate (1.5 ml) was filled in a vial flushed with nitrogen gas to obtain a fibrinogen-combined non-radioactive carrier as a pale yellow, transparent solution. The above operations were effected under a sterile condition. (C) Preparation of the ⁹⁹ m Tc-labeled, fibrinogen-combined dialdehydostarch-hexanediamine:KTS condensate condensation-reduction product as a radioactive diagnostic agent:- To the fibrinogen-combined non-radioactive carrier (1.5 ml) as obtained in (B), there was added a physiological saline solution (1.5 ml) containing ⁹⁹ m Tc (3.3 mCi) in the form of sodium pertechnetate, followed by stirring for 15 minutes to obtain the ⁹⁹ m Tc-labeled, figrinogen-combined polyacrolein-hexanediamine:KTS condensate condensation-reduction product useful as a radioactive diagnostic agent. This solution was pale yellow, transparent. (D) Properties of the radioactive diagnostic agent as obtained in (C):- The radioactive diagnostic agent as obtained in (C) was subjected to electrophoresis (1.7 mA/cm; 15 minutes) using a Veronal buffer (pH, 8.6) as a developing solvent and a cellulose acetate membrane as an electrophoretic membrane, and scanning was carried out by the use of a radiochromato-scanner. The radioactivity was recognized as a single peak at the locus of 0.5 cm distant from the original line towards the negative side. This locus was the same as that of the coloring band of fibrinogen with Ponceau 3R. From the above result, it may be said that the radioactive diagnostic agent as obtained in (C) has a labeling efficiency of nearly 100 % and its electric charge is substantially the same as that of fibrinogen. To the radioactive diagnostic agent as obtained in (C), 0.1 M sodium diethylbarbiturate hydrochloride buffer (pH, 7.3) containing 0.05 % calcium chloride to make a fibrinogen concentration of 1 mg/ml. Thrombin (100 units/ml; 0.1 ml) was added thereto. The resultant mixture was allowed to stand in an ice bath for 30 minutes. The produced fibrinogen clots were completely separated from the liquor, and radioactivity was measured on the clots and also on the liquor. From the obtained results, it was determined that the clottability of the radioactive diagnostic agent is 91 % based on the starting fibrinogen. Example 8 (A) Preparation of the dialdehydrostarch-deferoxamine condensation product as a non-radioactive carrier:- To a solution of deferoxamine (130 mg) in 0.01M phosphoric acid-0.15M sodium chloride buffer (1.5 ml), triethylamine (99 % solution; 27.9 µl) was added, and the resultant mixture was agitated at room temperature for 5 minutes. An aqueous solution of dialdehydrostarch (25 mg/ml; 2 ml) was added thereto. The resulting mixture was stirred at room temperature for 15 minutes to obtain a solution containing the dialdehydrostarch-deferoxamine condensation product which is useful as a non-radioactive carrier. (B) Preparation of the fibrinogen-combined dialdehydostarch-deferoxamine condensation product (a fibrinogen-combined non-radioactive carrier):- The non-radioactive carrier (5 ml) as obtained in (A) was added to a solution of human fibrinogen (200 mg) in 0.01M phosphate buffer-0.15M aqueous sodium chloride mixture (pH, 8.4) (30 ml) at 0 to 4°C, followed by stirring at the same temperature as above for about 3 hours. The reaction mixture was dialyzed to 0.01M glucose-0.35M sodium citrate solution at 0 to 4°C for 24 hours and then passed through a column of Sepharose®4B (diameter, 4.4 cm; height, 50 cm) using 0.01M glucose-0.35M sodium citrate solution as an eluting solvent. The eluate containing the fibrinogen-combined dialdehydostarch-deferoxamine condensation product was diluted with 0.01M glucose-0.35M sodium citrate solution to make a fibrinogen concentration of 1 mg/ml, and sodium ascorbate was added thereto to make a concentration of 30 mM. The resultant solution (3 ml) was admitted into each vial, followed by lyophilization to obtain a fibrinogen-combined, non-radioactive carrier as a cotton-like product. The above operations were effected under a sterile condition: Example 9 (A) Preparation of the dialdehydostarch-deferoxamine condensation product as a non-radioctive carrier:- To a solution of deferoxamine (130 mg) in 0.01M phosphate buffer-0.15M aqueous sodium chloride solution (1.5 ml), triethylamine (99 % solution) (27.9 µl) was added, and the resultant mixture was agitated at room temperature for 5 minutes. An aqueous solution of dialdehydrostarch (25 mg/ml; 2 ml) was added thereto, and stirring was continued at room temperature for 15 minutes to obtain a solution containing the dialdehydostarch-deferoxamine condensation product which is useful as a non-radioactive carrier. (B) Preparation of the fibrinogen-combined dialdehydostarch-deferoxamine condensation-reduction product (a fibrinogen-combined non-radioactive carrier):- The non-radioactive carrier (3.5 ml) as obtained above was added to a solution of fibrinogen (200 mg) in 0.01M phosphate-0.15M aqueous sodium chloride mixture (pH, 8.4) (30 ml) at 0 to 4°C, followed by stirring at the same temperature as above for about 3 hours. To the resulting mixture, sodium borohydride (12.9 mg) was added, and stirring was continued at 0 to 4°C for about 1 hour for reduction. To a portion of the reaction mixture, a solution of gallium citrate containing ⁶⁷Ga (1 mCi) was added for labeling, and the resultant solution was subjected to high speed liquid chromatography under the following conditions: Column: TSK-3000SW Solvent: 0.05M Tris-0.15M sodium chloride-hydrochloric acid buffer (pH 7.4) Pressure: 100 kg/cm² Flow rate: 1.0 ml/min Detection was made on the radioactivity of ⁶⁷Ga. As the result, the eluted pattern gave three peaks attributable to ⁶⁷Ga-labeled fibrinogen, the ⁶⁷Ga-labeled dialdehydrostarch-deferoxamine condensation-reduction product and ⁶⁷Ga-labeled deferoxamine. From the area ratio of the peak due to ⁶⁷Ga-labeled dialdehydrostarch-deferoxamine condensation reduction product and the peak due to ⁶⁷Ga-labelled deferoxamine, it was confirmed that 17.4 of the deferoxamine moieties are combined to one molecule of dialdehydostarch. Since the number of deferoxamine moieties in the fibrinogen-combined dialdehydrostarch-deferoxamine condensation-reduction product was confirmed to be 15.2 per one molecule of fibrinogen, the number of fibrinogen bonded to one molecule of dialdehydrostarch was calculated as about 0.9. The remainder of the reaction mixture was dialyzed to 0.01M glucose-0.35M sodium citrate solution at 0 to 4°C for 24 hours and then passed through a column of Sepharose® 4B (diameter, 4.4 cm; height, 50 cm) using the same solution as above as an eluting solvent. The eluate containing the fibrinogen-combined dialdehydostarch-deferoxamine condensation-reduction product was diluted with 0.01M glucose-0.35M sodium citrate solution to make a fibrinogen concentration of 1 mg/ml, and sodium ascorbate was added thereto to make a concentration of 30 mM. The resultant solution (3 ml) was filled in a vial, followed by lyophilization to obtain a fibrinogen-combined non-radioactive carrier as a cotton-like product. The above operations were effected under a sterile condition. The fibrinoge-combined non-radioactive carrier was dissolved in sterile water to make a fibrinogen concentration of 1 mg/ml, and a sufficient amount of an aqueous ferric chloride solution was added thereto to make a 1 : 1 complex between the deferoxamine moiety in said non-radioactive carrier and Fe(III) in said ferric chloride solution. The reaction mixture was allowed to stand for 1 hour and then subjected to measurement of absorbance at 420 nm using a solution of said non-radioactive carrier in sterile water as control, whereby the number of the deferoxamine moieties in said non-radioactive carrier was confirmed to be 15.2 per one molecule of fibrinogen. (C) Preparation of the ⁶⁷Ga-labeled, fibrinogen-combined dialdehydostarch-deferoxamine condensation-reduction product as a radioactive diagnostic agent:- To the fibrinogen-combined non-radioactive carrier as obtained in (B), an aqueous solution (2 ml) containing ⁶⁷Ga (2 mCi) in the form of gallium citrate was added to obtain the ⁶⁷Ga-labeled, fibrinogen-combined dialdehydostarch deferoxamine condensation-reduction product as a radioactive diagnostic agent. This solution was pale yellow, transparent and had a pH of about 7.8. (C') Preparation of the ⁶⁷Ga-labeled, fibrinogen-combined dialdehydostarch-deferoxamine condensation-reduction product as a radioactive diagnostic agent:- The non-radioactive carrier obtained in (B) was dissolved in sterile water, and human fibrinogen (0.5, 0.75, 1.0, 1.5, 2.0 or 3.0 mg) dissolved in 0.01M phosphoric acid-0.15M sodium chloride buffer (pH, 8.4) and 1 ml of an aqueous solution containing ⁶⁷Ga (1 mCi) in the form of gallium citrate were added thereto. The resulting mixture was allowed to stand at room temperature for 1 hour and then subjected to measurement of lebeling rate. In the same manner as above, the labeling rate of ⁶⁷Ga-labeled, fibrinogen-combined deferoxamine as prepared by labeling ⁶⁷Ga onto fibrinogen-combined deferoxamine was also measured. The results are shown in Table 3. As understood from the above, the non-radioactive carrier of the invention could be labeled with 100 % of ⁶⁷Ga (1 mCi) within 1 hour when 1 mg of fibrinogen was used. The conventional non-radioactive carrier (i.e. fibrinogen-combined deferoxamine) could be labeled only with 17.0 % of ⁶⁷Ga under the same condition as above. Even when 25.1 mg of fibrinogen were used, the conventional non-radioactive carrier is labeled with 83.5 % of ⁶⁷Ga at the most. It is thus appreciated that the non-radioactive carrier of the invention can afford a radioactive diagnostic agent having a higher relative radioactivity. Further, the radioactive diagnostic agent is useful in nuclear medical diagnosis aiming at detection of thrombosis. (D) Properties of the radioactive diagnostic agent as obtained in (C):- The radioactive diagnostic agent as obtained in (C) was subjected to electrophoresis (1.7 mA/cm; 15 minutes) using a Veronal buffer (pH, 8.6) as a developing solvent and a cellulose acetate membrane as an electrophoretic membrane, and scanning was carried out by the use of a radiochromato-scanner. The radioactivity was recognised as a single peak at the locus of 0.5 cm distant from the original line towards the negative side. This locus was the same as that of the coloring band of fibrinogen with Ponceau JR. From the above result, it may be said that the radioactive diagnostic agent as obtained in (C) has a labeling efficiency of nearly 100 % and its electric charge is substantially the same as that of fibrinogen. To the radioactive diagnostic agent as obtained in (C), 0.1M sodium diethylbarbiturate hydrochloride buffer (pH, 7.3) containing 0.05 % calcium chloride was added to make a fibrinogen concentration of 1 mg/ml. Thrombin (100 units/ml; 0.1 ml) was added thereto. The resultant mixture was allowed to stand in an ice bath for 30 minutes. The produced fibrinogen clots were completely separated from the liquor, and radioactivity was measured on the clots and also on the liquor. From the obtained results, it was determined that the clottability of the radioactive diagnostic agent is 89 % based on the starting fibrinogen. (E) Behaviors of the radioactive diagnostic agent obtained in (C) in rats:- The radioactive diagnostic agent as obtained in (C) (0.2 ml) was administered intravenously to each of female rats of SD strain, and the variations of the blood level and the organ distribution with the lapse of time were recorded. The results are shown in Table 4. Table 4 (Distribution in rat body; %/g) The extremely high blood level over a long period of time and the figure of distribution into various organs of the radioactive diagnostic agent as shown in Table 4 are quite similar to those of ¹³¹I-labeled fibrinogen as conventionally employed. (F) Behaviors of the radioactive diagnostic agent obtained in (C) in thrombosed rabbits:- Thrombosis was produced in rabbits at the femoral part by the formalin application procedure. To the rabbits, the radioactive diagnostic agent (0.5 ml) obtained in (C) was administered through the ear vein. After 24 hours from the administration, a constant amount of the blood was sampled, and the locus of thrombosis was taken out. Radioactivity was measured on the blood and the locus of thrombosis. The radioacitivity ratio of the locus of thrombosis to the blood for the same weight was 8.63 ± 3.83 (average in 10 animals ± S.D. value). From the above results, it is understood that the radioactive diagnostic agent obtained in (C) has the nearly same physiological activity as fibrinogen does. Thus, the radioactive diagnostic agent is useful for nuclear medical diagnosis. (G) Toxicity of the radioactive diagnostic agent obtained in (C):- The radioactive diagnostic agent obtained in (C) was subjected to attenuation of the radioactivity to an appropriate extent, and the resultant product was administered intravenously to groups of male and female rats of SD strain, each group consisting of five animals, at a dose of 1 ml per 100 grams of the bodyweight (corresponding to 600 times the expected dose to human beings) and also to groups of male and female mice of ICR strain, each group consisting of five animals, at a dose of 0.5 ml per 1.0 gram of the bodyweight (corresponding to 3,000 times the expected dose to human beings). As the control, the same volume of a physiological saline solution as above was intravenously administered to the separate groups of the same animals as above. The animals were fertilized for 10 days, and the variation in bodyweight during that period was recorded. No significant difference was recognized between the medicated groups and the control groups. After 10 days from the administration, all the animals were sacrificed and subjected to observation of the abnormality in various organs. No abnormality was seen in any of the animals. From the above results, it may be said that the toxicity of the non-radioactive carrier of the invention is extremely low. Example 10 (A) Preparation of dialdehydodextran-deferoxamine condensation-reduction product as a non-radioactive carrier:- To a solution of deferoxamine (2.8 g) in water (30 ml), an equimolar amount of triethylamine (432 mg) was added, followed by stirring at room temperature for 10 minutes. The resultant solution was added to a solution of dialdehydodextran (1 g; aldehyde group content, 5.1 µmole/mg) in water (40 ml), followed by stirring at room temperature for 15 minutes. To the reaction mixture, sodium borohydride (167 mg) was added, and stirring was continued at room temperature for about 1 hour. The resulting solution was admitted in a cellulose tube and dialyzed to water for 3 days, followed by gel chromatography under the following conditions: Carrier: Sephadex® G-50 Solvent: water Column: diameter, 4.5 cm; height, 50 cm Flow rate: 2.5 ml/min The dialdehydodextran-deferoxamine condensation-reduction product was eluted at a volume of 300 to 450 ml, while the unreacted deferoxamine was eluted at a volume of 550 to 600 ml. The eluate containing said condensation-reduction product was lyophilized. The lyophilized product was subjected to analysis with high speed liquid chromatography under the following conditions: Column: TSK-3000SW Solvent: 0.05M Tris-0.15M sodium chloride-hydrochloric acid buffer (pH, 7.4) Pressure: 100 kg/cm² Flow rate: 1.0 ml/min Absorptive wavelength: 280 nm As the result, said condensation-reduction product was confirmed to show a retention volume of 27.3 ml. No free deferoxamine was detected. (The retention volume of deferoxamine in the above system is 32.8 ml.) (B) Preparation of the fibrinogen-combined dialdehydrodextran-deferoxamine condensation-reduction product (a fibrinogen-combined, non-radioctive carrier):- Into a solution of dialdehydodextran (127 mg) in 0.01M phosphate buffer-0.15M aqueous sodium chloride mixture (5 ml), deferoxamine (370 mg) was dissolved, and triethylamine (78.9 µl) was added thereto, followed by stirring at 10 to 15°C for 20 minutes. The resulting solution was added to a solution of fibrinogen (400 mg) in 0.01M phosphate buffer-0.15M aqueous sodium chloride solution (40 ml) at 10 to 15°C, followed by sitrring at the same temperature as above for about 2 hours. To the reaction mixture, sodium borohydride (12,3 mg) was added, and stirring was continued at 10 to 15°C for about 1 hour. The resulting mixture was dialyzed to 0.01M glucose-0.35M sodium citrate solution at 0 to 4°C for 3 days and then passed through a column of Sepharose®CL-6B (diameter, 4.4 cm; height, 100 cm) using the same solution as above as a eluting solvent. The eluate was diluted with 0.01M glucose-0.35M sodium citrate solution to make a fibrinogen concentration of 1 mg/ml, and sodium ascorbate was added to make a concentration of 30mM. The resultant solution (3 ml) was filled in a vial, followed by lyophilization to obtain a cotton-like product, which is useful as a fibrinogen-combined non-radioactive carrier. The above operations were effected under a sterile condition. (C) Preparation of the ⁶⁷Ga-labeled, fibrinogen-combined dialdehydodestran-deferoxamine condensation-reduction product as a radioactive diagnostic agent:- To the fibrinogen-combined non-radioactive carrier obtained in (B), an aqueous solution (2 ml) containing ⁶⁷Ga (2 mCi) in the form of gallium citrate was added to obtain the ⁶⁷Ga-labeled, fibrinogen-combined dialdehydostarch deferoxamine condensation-reduction product useful as a readioactive diagnostic agent. This solution was pale yellow, transparent and had a pH of about 7.8. (D) Properties of the radioactive diagnostic agent as obtained in (C):- The radioactive diagnostic agent as obtained in (C) was subjected to electrophoresis (1.7 mA/cm; 15 minutes) using a Veronal buffer (pH, 8.6) as a developing solvent and a cellulose acetate membrane as an electrophoretic membrane, and scanning was carried out by the use of a radiochromato-scanner. The radioactivity was recognized as a single peak at the locus of 0.5 cm distant from the original line towards the negative side. This locus was the same as that of the coloring band of fibrinogen with Ponceau 3R. From the above result, it may be said that the ⁶⁷Ga-labeled, fibrinogen-combined dialdehydodextran-deferoxamine condensation-reduction product has a labeling efficiency of nearly 100 % and its electric charge is substantially the same as that of human fibrinogen. To the radioactive diagnostic agent as obtained in (C), 0.1M sodium diethylbarbiturate hydrochloride buffer (pH, 7.3) containing 0.05 % calcium chloride was added to make a fibrinogen concentration of 1 mg/ml. Thrombin (100 units/ml; 0.1 ml) was added thereto. The resultant mixture was allowed to stand in an ice bath for 30 minutes. The produced fibrinogen clots were completely separated from the liquor, and radioactivity was measured on the clots and also on the liquor. From the obtained results, it was determined that the clottability of the radioactive diagnostic agent is 84 % based on the starting fibrinogen. Example 11 (A) Preparation of the dialdehydostarch-deferoxamine condensation product as a non-radioactive carrier:- Into a solution of dialdehydostarch (10 mg) in 0.03M phosphate buffer-0.15M aqueous sodium chloride mixture (1.0 ml), deferoxamine (23 mg) was dissolved at room temperature. After addition of triethylamine (5.2 µl), stirring was continued at 12 to 15°C for 20 minutes to obtain a solution containing the dialdehydostarch-deferoxamine condensation product useful as a non-radioactive carrier. (B) Preparation of the 19-9 F(ab')₂ fragment-combined dialdehydostarch-deferoxamine condensation product (a 19-9 F(ab') 2 fragment-combined non-radioactive carrier):- The non-radioactive carrier (0.42 ml) as obtained in (A) was added to a physiological saline solution of 19-9 F(ab')₂ fragment (i.e. F(ab') 2 fragment of monoclonal anti-human colorectal carcinoma antibody 19-9; concentration, 18 mg/ml) (0.55 ml), followed by stirring at 4 to 6°C for about 2 hours. After addition of sodium borohydride (3 mg), stirring was continued at 4 to 6°C for about 1 hour. The reaction mixture was dialyzed to 0.05M phosphate buffer-0.15M aqueous sodium chloride mixture (pH, 5.5) at 4 to 6°C for 24 hours and then passed through a column of Sephadex® G-150 Superfine (diameter, 2.2 cm; height, 30 cm) using 0.05M phosphate buffer-0.15M aqueous sodium chloride mixture as an eluting solvent. The resultant solution was diluted with the same solution as the eluting solvent to make a 19-9 F(ab')₂ fragment concentration of 0.5 mg/ml, and sodium ascorbate was added thereto to make a concentration of 100 mM, whereby a 19-9 F(ab')₂ fragment-combined non-radioactive carrier was obtained as a pale yellow transparent solution. (C) Preparation of the ⁶⁷Ga-labeled, 19-9 F(ab')₂ fragment-combined dialdehydostarch-deferoxamine condensation product as a radioactive diagnostic agent:- To the 19-9 F(ab')₂ fragment-combined non-radioactive carrer (1 ml) as obtained in (A), a solution (0.5 ml) containing ⁶⁷Ga (0.5 mCi) in the form of gallium citrate was added to obtain the ⁶⁷Ga-labeled, 19-9 F(ab')₂ fragment-combined dialdehydostarch-deferoxamine condensation product as a pale yellow transparent solution, which is useful as a radioactive diagnostic agent. (D) Properties of the radioactive diagnostic agent as obtained in (C):- The radioactive diagnostic agent as obtained in (C) was subjected to electrophoresis (1 mA/cm, 30 minutes) using Beronal buffer (pH, 8.6) as a developing solvent and a cellulose acetate membrane as an electrophoretic membrane, and scanning was carried out with a radiochromato-scanner. Radioactivity was recognized as a single peak at the locus of 1.1 cm distant from the original line towards the negative side. This locus was the same as the coloring band of the 19-9 F(ab')₂ fragment with Ponceau 3R. From the above result, it is understood that the radioactive diagnostic agent has a labeling rate of nearly 100 % and its electrostatic state is substantially equal to that of the 19-9 F(ab')₂ fragment.

Claims: A non-radioactive carrier which comprises (1) the unit of a polyformyl compound having at least three formyl groups per molecule, and (2) at least two units of an amino group-containing chelating compound bonded to the polyformyl compound with intervention of a methyleneimine linkage (-CH=N-) or a methyleneamine linkage ( -CH₂NH- ) formed by the condensation between the formyl group in the polyformyl compound and the amino group in the chelating compound, optionally followed by reduction. The non-radioactive carrier according to claim 1, wherein the polyformyl compound is polyacrolein. The non-radioactive carrier according to claim 2, wherein the polyacrolein comprises 3 to 4000 units of acrolein. The non-radioactive carrier according to claim 1, wherein the polyformyl compound is a poly(dialdehydosaccharide). The non-radioactive carrier according to claim 4, wherein the poly(dialdehydosaccharide) is dialdehydostarch. The non-radioactive carrier according to claim 4, wherein the poly(dialdehydosaccharide) is dialdehydodextran. The non-radioctive carrier according to claim 4, wherein the poly(aldehydosaccharide) is dialdehydoamylose. A radioactive diagnostic agent comprising the non-radioactive carrier according to claims 1-7 and further comprising at least one unit of an amino group-containing physiologically active substance bonded to the polyformyl compound with intervention of a methyleneimine linkage or a methyleneamine linkage formed by the condensation between the formyl group in the polyformyl compound and the amino group in the physiologically active substance, optionally followed by reduction, and at least two radioactive metallic elements of which each is bonded to the chelating compound through a chelating bond. A physiologically active substance-combined non-radioactive carrier according to claims 1-7 which comprises (1) the unit of a polyformyl compound having at least three formyl groups per molecule, (2) at least two units of an amino group-containing chelating compound bonded to the polyformyl compound with intervention of a methyleneimine linkage (-CH=N-) or a methyleneamine linkage (-CH₂NH-) formed by the condensation between the formyl group in the polyformyl compound and the amino group in the chelating compound, optionally followed by reduction, and (3) at least one unit of an amino group-containing physiologically active substance bonded to the polyformyl compound with intervention of a methyleneimine linkage or a methyleneamine linkage formed by the condensation between the formyl group in the polyformyl compound and the amino group in the physiologically active substance, optionally followed by reduction. A process for preparing a non-radioactive carrier according to claim 1 which comprises condensing a polyformyl compound having at least three formyl groups per molecule with an amino group-containing chelating compound to form an iminomethylene linkage between the formyl group in the former and the amino group in the chelating compound, optionally followed by reduction of the iminomethylene linkage to an aminomethylene linkage. A process for preparing a physiologically active substance-combined non-radioactive carrier according to claim 1 which comprises condensing the non-radioactive carrier according to claim 10 with an amino group-containing physiologically active substance to form an iminomethylene linkage between the formyl group in the polyformyl moiety of the non-radioactive carrier and the amino group in the chelating compound, optionally followed by reduction of the iminomethylene linkage to an aminomethylene linkage. A process for preparing a physiologically active substance-combined polyformyl compound according to claim 9 which comprises condensing a polyformyl compound having at least three formyl groups per molecule with an amino group-containing physiologically active substance to form an iminomethylene linkage between the formyl group in the former and the amino group in the physiologically active substance, optionally followed by reduction of the iminomethylene linkage to an aminomethylene linkage. A process for preparing a physiologically active substance-combined non-radioactive carrier according to claim 9 which comprises condensing the physiologically active substance-combined polyformyl compound according to claim 12 with an amino group-containing chelating compound to form an iminomethylene linkage between the formyl group in the polyformyl moiety of the physiologically active substance-combined polyformyl compound and the amino group in the chelating compound, optionally followed by reduction of the iminomethylene linkage to an aminomethylene linkage. A process for preparing a radioactive diagnostic agent according to claim 8 which comprises labeling the physiologically active substance-combined non-radioactive carrier according to claim 11 and 13 with a radioactive metallic element. A chemical Product which comprises (1) the unit of a polyformyl compound having at least three formyl groups per molecule, (2) at least two units of an amino group-containing chelating compound bonded to the polyformyl compound with intervention of a methyleneimine linkage (-CH=N-) or a methyleneamine linkage (-CH₂NH-) formed by the condensation between the formyl group in the polyformyl compound and the amino group in the chelating compound, optionally followed by reduction, (3) at least one unit of an amino group-containing physiologically active substance bonded to the polyformyl compound with intervention of a methyleneimine linkage or a methyleneamine linkage formed by the condensation between the formyl group in the polyformyl compound and the amino group in the physiologically active substance, optionally followed by reduction, and (4) at least two radioactive metallic elements of which each is bonded to the chelating compound through a chelating bond. A chemical product which comprises (1) the unit of a polyformyl compound having at least three formal groups per molecule, and (2) at least two units of an amino group-containing chelating compound bonded to the polyformyl compound with intervention of a methyleneimine linkage (-CH=N-) or a methyleneamine linkage (-CH₂NH-) formed by the condensation between the formyl group in the polyformyl compound and the amino group in the chelating compound, optionally followed by reduction. A physiologically active substance-combined product which comprises (1) the unit of a polyformyl compound having at least three formyl groups per molecule, (2) at least two units of an amino group-containing chelating compound bonded to the polyformyl compound with intervention of a methyleneimine linkage (-CH=N-) or a methyleneamine linkage ( -CH₂NH- ) formed by the condensation between the formyl group in the polyformyl compound and the amino group in the chelating compound, optionally followed by reduction, and (3) at least one unit of an amino group-containing physiologically active substance bonded to the polyformyl compound with intervention of a methyleneimine linkage or a methyleneamine linkage formed by the condensation between the formyl group in the polyformyl compound and the amino group in the physiologically active substance, optionally followed by reduction.

Inventors: HAZUE, MASAAKI, TAKAHASHI, KEIETSU NIHON MEDI-PHYSICS CO., LTD., UEDA, NOBUO
Applicants: NIHON-MEDI PHYSICS CO., LTD.
Application year: 1983
Main classification: A61K49
IPC codes: A61K47, A61K51