BACKGROUND OF THE INVENTION

Modern clinical medical practice along with advances in industrial technology and manufacturing has created a need for sophisticated non-invasive imagining technologies. The response to this need has been met by the marriage of radiology and computers. The net result has been an imaging technological revolution.

A product of this revolution has been the technology of magnetic resonance imagining (MRU . The origin of MRI lies in nuclear magnetic resonance (NMR) technology which has been used for years as a means of chemical analysis. This technology has been subsequently refined and combined with computer technology in which electromagnetic fluctuations are resolved and presented in an imaging format. This emerging technology has become known as magnetic resonance imaging in the art. The MRI technique has become a valuable imaging modality in particular for biomedical usages. MRI in biomedical applications relies on low energy radiation or radio waves to probe the organs and tissues deep inside the human body with high resolution as opposed to computerized tomography (CT) and x-ray technology which rely on high energy radiation or electromagnetic pulses targeted at the organ systems to be examined. In this regard, MRI has proven more effective than CT and x-rays in providing detailed information on both the structure and function of tissues, in that biologic tissues are relatively transparent to x-rays.

For example, MRI technology can distinguish different tissue types or detect tissues whose biochemical environments may have been altered due to a disease process. MRI also provides a means to examine and diagnose with high resolution, specificity, and detail, the internal structures, organs and disease processes of the body in a dynamic format. Furthermore the lack of definitively known hazards associated with low levels of magnetic and radio-frequency fields permits repeated scans along any plane, including, but not limited to, transverse, coronal and sagittal sections.

MRI technology utilizes the property that each atomic species has its own characteristic magnetic moment. In the case where there is an even number of protons or neutrons, or the particles are paired in a given species, the magnetic potential is statistically canceled out. However, nuclei of certain atoms and isotopes which are unpaired or have an odd number of protons or neutrons possess an intrinsic spin. A potential magnetization occurs from the rapid spinning of the unpaired particle. Species which satisfy this parameter, among others, are phosphorus-31, carbon-13, sodium-23, fluorine-19, oxygen-17 and hydrogen-1 and can be used in MRI studies. Consequently, ^: H protons -and water which encompass many biochemical processes and tissues are often the atomic species of choice to produce revealing in-depth images of the body. In practice in MRI technology, a magnetic field of a given strength (B, expressed generally in units of gauss or telsa) is applied to the target area of investigation. The"MRI technician can manipulate the magnetic field environment so that only protons at very specific sites are affected. The magnetic nuclei of the various atomic species in the target area line up or specifically orient relative to the magnetic field according to their allowed quantum mechanic states. In the case of a proton, the principle isotope of hydrogen, there are two allowable states of orientation — parallel (low energy) or anti-parallel (high energy) to the magnetic field.

A radio wave pulse is also directed at the atomic species in the target area. The atomic species or protons within a given magnetic field have a characteristic magnetic

moment. These atomic species or protons will resonate upon absorption of a pre-designated energy input from a specific characteristic radio frequency. The characteristic frequency at which resonance occurs for an atomic specie under a given magnetic field is known as the Larmor frequency. In this instance, resonance is the act of the atomic species to absorb and emit energy repeatedly and rapidly. Thus the infusion of energy from the radio waves with the magnetic field causes the atomic species to reorient in the magnetic field due to the changes in energy state and subsequently leads to oscillation between the various energy states.

This oscillating activity or resonance signal of the atomic species can be detected by a radio receiver. This information is then integrated with the measurable period of time or relaxation that it takes the species, often ^X H atoms, to lose the energy that was absorbed by the directed pulses. Since a ^α H proton has predictable atomic activity, any variances in behavior are due to the local biochemical environment of the proton. Thus the patterns and characteristics of the resonance signals can be converted into an image to reflect the biochemical environment surrounding the target area.

One of the measurements of relaxation in this process is the spin-lattice, thermal or longitudinal relaxation time (Tl) . This measurement reflects the characteristic time it takes the excited nuclei to return to the ground state by dissipating the excess energy to the surroundings or lattice field. The dissipation process is dependent on many factors which include but are not limited to the Larmor frequency, the magnetic field strength, the size of the molecule, and the biochemical environment. Relaxation times have been measured for various fluids, organs and tissues in different species of mammals. Investigations have shown that tissues containing more water have longer Tl relaxation times, whereas those containing lipid or paramagnetic species have the capacity to shorten Tl. This is significant because in various instances, shorter Tl times have resulted in higher signal intensities and therefore brighter image enhancement. Thus a skilled practitioner can change many of the variables to enhance or improve the image of

the voxel or volume element of the species under examination. See Stark, D.D. and W.G. Bradley (eds.). 1992. Magnetic Resonance Imaging (Second edition. Volumes One and Two. Mosby, St. Louis), which is incorporated herein by reference. Another of the measurements of relaxation is spin-spin or transverse relaxation time (T2) . This measurement reflects the characteristic time it takes the nuclei in various states of excitation to exchange energy with each other as opposed to the lattice which results in a loss of magnetization. The magnetic decay is due to the various nuclear magnetic moments being out of phase with each other or dephasing as a result of their mutual interaction. This phenomena is a direct consequence of magnetic field imperfections and resultant generated fields in the biological system under investigation which cause the nuclei to precess at slightly different rates. This loss of phase coherence leads to a loss of magnetization. The spin-spin or transverse relaxation time (T2) is a means to measure the loss of magnetization. Investigations have shown that large macromolecules and water molecules which bind to macromolecules reorient or tumble more slowly than small molecules causing efficient T2 relaxation. By contrast such molecules which tumble at rates much slower than the Larmor frequency result in inefficient Tl relaxation.

A simplified expression that describes MRI signal intensity in terms of the parameters of relaxation is the following:

SI = N(H) [l-e-** ]β- ^w ™ wherein

SI = signal intensity

N(H) = the spin density, the density of resonating spins (e.g. number of protons) in a given volume (e.g. a discrete volume of tissue)

TR = repetition time, the time between the beginning of one radio frequency pulse sequence and the beginning of the succeeding pulse sequence at a specified tissue location

TE = echo time delay, which is the time between the center of the 90-degree pulse and the center of the spin echo

Tl s spin-lattice relaxation time

T2 = spin-spin relaxation time.

The above expression delineates that signal intensity will increase when N(H) increases, Tl decreases, or T2 increases. Alternatively, the signal intensity will decrease when N(H) decreases, Tl increases or T2 decreases. Thus Tl and T2 times have reciprocal effects on image intensity. The above parameters play an intrinsic role in the dynamics of the imaging process.

The altering effects on Tl and T2 are critically dependent on the magnetic entities and the concentrations thereof utilized in an imaging agent. Paramagnetic materials reduce both Tl and T2, however the effects on Tl predominate, particularly at low concentrations. This means that they are best detected using Tl weighted techniques. Conversely, ferromagnetic and superparamagnetic entities rely on T2 weighted imaging.

The relationship between the concentration of an MRI imaging agent or its magnetic entity is distinctly non-linear. This phenomena is distinctly different from radiographic contrast agents in which signal intensity depends linearly on the concentration of the material present. As a consequence, the signal intensity or conspicuity of an MRI agent represents the net effect of the positive and negative contributions of Tl and T2 which are both concentration dependent. For example, in the case of the paramagnetic specie, gadolinium, the contribution of Tl predominates at low concentrations, whereas when the concentration increases, the effects of T2 become more pronounced. Thus, as gadolinium concentration increases, an initial threshold level is met at which imaging becomes possible. This is followed by a continual increase in signal intensity with increasing gadolinium concentration until an

optimal threshold is met at which point the contributions of T2 result in a diminishing of signal intensity or conspicuity.

A common means to improve imaging is through the use of contrast agents, which alter the above described parameters. These agents increase and clarify the information content of diagnostic images. Contrast agents enhance a diagnostic image by altering the image contrast or the difference in signal intensity between the different biochemical environments (e.g. tissues) . In MRI, the contrast agents work by altering the local magnetic environment of tissues primarily by altering tissue relaxation rates. The contribution of various contrast agents has been attributed to the interaction of unpaired electrons of the contrast agent and the hydrogen nuclei of water molecules. A theoretical explanation of the effects of these interactions has indicated that the distance from the center of the paramagnetic species of the contrast agent to the center of the hydrogen nucleus undergoing relaxation is critical. This theoretical work indicates that relaxation times are proportional to the distance raised to the 6th power. Thus changes in signal intensity are dependent on the ability of the paramagnetic species of the contrast agent to approach the protons of the sample being examined. See Chapter 14, "Contrast Agents" in Stark and Bradley and Chapter 6, "MRI:New Breakthroughs in Medical Diagnosis" in Science at the Frontier, Volume 1 by Addison Greenwood, National Academy Press, Washington, D.C. 1992, which are incorporated herein by reference.

Historically, magnetic materials were shown to affect the relaxation times of resonating protons. The early work concentrated on paramagnetic ferric ions in solution. This work was later extended to a variety of paramagnetic transition metals. Subsequently, the research led to the use of paramagnetic ions and chelate complexes to alter relaxation times. This line of research resulted in the first commercial MRI contrast agent, Gadolinium-Diethylenetriaminepentaacetic Acid-Dimeglumine ( [NMG] ₂ Gd-DTPA] ) or Gadiopentetate Dimeglumine.

The most recent work has focused on attempts to associate metal chelate complexes with large molecular weight entities such as macromolecules to improve relaxivity. These macromolecules also serve as vehicles of transport and include but are not limited to oligopeptides, proteins, lipids, polysaccharides, and synthetic polymers. Furthermore, in this regard, attempts have been made to combine the metal chelate complexes with macromolecules such as monoclonal antibodies to provide target-specific imaging. Optimal relaxation enhancement, which results in improved imaging, occurs when molecules or tissues bearing nuclear spins have fast access to as many sites near the paramagnetic molecule as possible. This effect can be amplified by increasing the concentration or number of metal ions per macromolecule by polymerization. The addition of a metal ion to a chelating agent reduces the number of effective bonding and interaction sites.

To be an effective contrast agent, the metal chelate complex must be stable. Increased stability of the complex results by multiple bond formation between the chelating agent and the metal ions. Thus, the stability is a function of the number of bonding sites of the chelating agent, the coordination number of the metal ion, steric factors and the biochemical environment, The stability of the metal chelate complex and its toxicity are intimately related. This is due to the fact that excessive quantities of transition and Lanthanide metals can be toxic. A stable metal chelate complex prevents the presence of free metal ions and shields the toxic effects of bonded metal ions. Thermodynamic stability of the complex is also important in that a free metal ion and a free ligand tend to be more toxic than the resulting metal complex. In addition, a thermodynamically stable metal chelate complex will hinder metal ion substitution in vivo and chelate dissociation. Finally, a thermodynamically stable metal chelate complex can alter or reduce metabolic attack which could result in the release of toxic metabolites.

Another factor for providing effective contrast agents is the biodistribution and pharmacokinetics of the metal chelate

complexes. Since the complexes have toxic components, the uptake and clearance of these compounds from the targeted site of examination is critical. This is particularly true for susceptible organ systems. The biodistribution and transport kinetics characteristics of these compounds are also important in that these parameters affect the time period in which effective imaging can occur. Thus, contrast agent compounds are often organ specific in their effectiveness.

All agents proposed up to now for imaging diagnosis, which consist of complexes of heavy metals, are not very satisfactory with regard to their practical use in man, or create more or less serious problems with regard to relaxivity and tolerance. Also, they frequently exhibit insufficient selectivity of the bond with the heavy metal, insufficient stability, and particularly, lack of selective targeting to certain organs.

Another problem is the tendency of many complexes to exchange the central metal ion for trace metals which are essential to the organism, or for ions, for example, Ca* ² , which in vivo are present in relatively large amounts. In the case of insufficient specific stability of the complex, trace metals of vital importance may, in fact, be extracted from the organism. In their place, undesirable heavy metals, such as gadolinium, may be deposited in their place, which may remain in the organism for a long time. Particularly problematic is the use of these complexes in dosages which would be suitable or desirable for imaging diagnosis.

With regards to synthesizing contrast agents, the preparation of MRI contrast agents utilizing the conjugation of macromolecules with chelated polymer carriers (Sieving, 1990) includes operations with water and air-sensitive reagents. This has been difficult to achieve for milligram quantities of reagents. Moreover, these prepared conjugates have a low stability within the living cell, which can limit their in vivo utility for MRI.

Besides stability problems, previous methods have also been unsuccessful in binding a sufficiently effective number of atoms of a contrast metal (paramagnetic atoms) to a chelating

agent to be clinically useful in an imaging technology, such as MRI.

With respect to the above shortcomings, there therefore exists an urgent and unfulfilled need for contrast agents which are stable for in vivo usage. These contrast agents would also ideally possess a sufficiently concentrated number of bound or complexed paramagnetic atoms of a contrast metal. This number of concentrated atoms advantageously exceeds the threshold level required for visualization in MRI. Such contrast agents would be ideal for clinical image. Such useful clinical agents would then be of significant commercial value to the medical community as a diagnostic tool for differentiating and identifying diseased tissue from normal tissue.

Furthermore, there is a need for effective contrast agents which avoid the toxicity and stability problems inherent in using gadolinium. Further, there is a need for new and improved contrast agents, whether they include gadolinium, or another paramagnetic metal in place of gadolinium.

In another respect, the combination of some metal chelate complexes with macromolecules has resulted in diminished biological activity of the macromolecules. It has been theorized that the combination has altered the chemistry or steric factors of the macromolecules. This alteration has resulted in diminished biological activity. Thus, there is also an urgent need for target-specific contrast agents which are conjugated with macromolecules, e.g., antibodies, for specific targeting to receptor or antigenic sites, which targeting macromolecules advantageously retain their biological or immunological activities in vivo.

SUMMARY OF THE INVENTION

The present invention addresses and fulfills the above-described needs. The present invention, as described further below with more particularity, addresses and advantageously fulfills the need in the art for stable, safe, and clinically useful contrast agents for imaging technologies, particularly for, but not limited to, MRI.

The present invention advantageously provides contras agents for imaging, especially for, but not limited to MRI, and for additional applications in various non-imaging technologies. These other applications include diagnostic, monitoring, markin and mapping.

The contrast agent of the present invention, which advantageously and unexpectedly enhances visualization in imaging procedures, is comprised of a conjugate of a carrier with a chelating agent. The conjugate is complexed with an effective number of atoms of a paramagnetic metal. An effectiv number of atoms is defined as that number which enhances signal intensity or enhances the visualization of an image. The contrast agent of the present invention unexpectedly possesses an increase in conspicuity or enhanced contrast, which increase clearly enhances signal intensity or visualization. Such visual enhancement encompasses either a positive or negative contrast.

A further aspect then of the present invention is a composition which is comprised of the contrast agent of the present invention and a pharmaceutically-acceptable carrier. Another aspect of the present invention is a method for synthesizing the contrast agents of the present invention. The method of the invention is unexpectedly simpler and more efficient than other currently available techniques. The method is also more economical. The method unexpectedly provides a clinically useful amount of a contrast agent having a higher concentration of bound paramagnetic atoms than previously achieved. The method of the invention for synthesizing a contrast agent comprises conjugating a carrier with a chelating agent, and complexing the conjugate with an effective number of atoms of a paramagnetic metal. The method therefore provides the contrast agents of the invention having a favorable increase in conspicuity or enhanced signal intensity.

Another aspect of the present invention advantageousl provides a method for further conjugation of the contrast agents of the present invention with proteins or other macromolecules for specific organ or tissue targeting, without adversely affecting the biological activity of these macromolecules.

Another aspect of the present invention is a kit for use by, e.g., a clinician or diagnostician. The kit comprises a package which contains separate containers for the contrast agents of the present invention in a form and dosage suitable for administration, and an appropriate diluent or carrier. Alternatively, the kit may provide separate containers of reagents for making the contrast agents of the invention by way of the method of the present invention.

The resulting novel contrast agents have many unexpected properties which make them particularly advantageous, such as beneficial imaging properties, low toxicity, high stability, advantageously selective biodistribution or targeting characteristics, and safer degradation and excretion.

Furthermore, the contrast agents of the present invention form advantageously stable, safe, and effective pharmaceutical compositions for administering or using in vivo in mammals, including humans, in MRI and other suitable imaging technologies.

The application of the contrast agents is not limited to imaging procedures. The contrast agents of the invention are also advantageously suitable for application or use in a wide variety of fields which encompass non-imaging technologies.

The contrast agents in accordance with the present invention unexpectedly reduce or prevent the toxic effects of contrast-enhancing paramagnetic metals, while enhancing signal intensity or conspicuity. The contrast agents of the present invention thus advantageously possess very low biological toxicity. This is so despite having a higher concentration of paramagnetic atoms bound per molecule than heretofore achieved by any other contrast agent. In addition, the agents unexpectedly possess substantially better relaxation properties than other contrast agents, which permits the use of a smaller amount of the agents of the invention to achieve the same or similar effect. The contrast agents of the present invention unexpectedly provide a favorable biochemical environment for close and efficacious interaction of the paramagnetic species

and the targeted body system. This is achieved while preserving the stability and structural integrity of the contrast agents.

The contrast agents of the present invention are advantageously useful as MRI agents, agents for cancer detection, diagnosis of dementia and psychiatric disease, and for tracing of neuronal pathways and body mapping.

These and other features, aspects, and advantages of the present invention will become better understood with regard to the following description, accompanying drawings and appended claims.

BRIEF DESCRIPTION OF THE FIGURES

Figure 1 shows a sample image from a T _: relaxation experiment of multiple test tubes containing solutions prior to selection for in vivo use based on signal intensity. The bottom tube contains the contrast agent of the present invention, which shows a sharp signal intensity.

Figure 2 shows a coronal image of a cat injected via the left ventricle with the contrast agent of the present invention conjugated with antibody to antigen 301. The white material (arrows) indicates the location of the contrast agent.

Figure 3 shows an axonal tracing (arrows) in a cat brain utilizing a contrast agent of the present invention which is a wheat germ agglutinin-gadolinium conjugate.

Figure 4 shows a magnified view of the axonal tracing shown in Figure 3.

Figure 5 shows a fluorescence microscopy photograph which white material (arrows) is histologic confirmation of the presence of the contrast agent of the present invention in the cat brain. DETAILED DESCRIPTION OF THE INVENTION

ABBREVIATIONS

DOTA: 1, 4, 7, 10-tetraazacyclododecane-N, N' , N' ' , N'''- tetraacetic acid: was prepared from cyclen (Aldrich, #33,965-2) according to Desreux (1980); DTPA: Diethylenetriaminepentaacetic acid (Aldrich, #28,556- 0);

EDAC: l-Ethyl-3-(3-dimethylaminopropyl)-carbodiimide hydrochloride (Sigma, #E6383);

EDTA: Ethylenediaminetetraacetic acid;

PL: Poly-d-lysine hydrobromide, MW 15,000-30,000, degree of polymerization - 100 (Sigma, #P4408) ;

WGA: Wheat germ agglutinin; lectin triticum vulgaris (Sigma, #L9640) .

The contrast agent of the present invention for enhancing visualization in imaging or for use in non-imaging applications is a conjugate of a carrier with a chelating agent. Additionally, the conjugate is complexed with a visually enhancing number of atoms of a suitable paramagnetic metal. The contrast agents advantageously and unexpectedly possess an overall increase in conspicuity. Such an increase in conspicuity favorably enhances visualization of an image, for example, in MRI. For purposes of the present invention, visual enhancement of an image is defined as either a positive or negative contrast. Conspicuity may be defined as the ability to detect the area which is enhanced by the contrast agents of the present invention relative to the background tissue.

Conspicuity is a measure of the relative signal intensity of the area of interest relative to the rest of the tissue, taking into account background signal intensity due to noise. Accordingly, conspicuity is a measure of enhanced or improved contrast of an image or signal intensity obtained by way of the contrast agents of the present invention.

The reactants for making the contrast agents of the invention are generally known compounds, and otherwise are routinely prepared by techniques within the skill of the chemist.

The group of suitable carriers for conjugation with chelating agents for the synthesis of the contrast agents of the present invention is broad and includes, but is not limited to, oligopeptides, proteins, lipids, polysaccharides, dextran polymers and synthetic polymers.

Any protein is considered suitable as a carrier. A group of particularly suitable protein carriers is comprised of

a polymer or copolymer of polyamino acids. Preferred are polymers or copolymers of basic amino acids such as polylysine and polyornithine. To protect the contrast agents of the invention over longer periods of time from protease degradation, such as by ubiquitin, the d-isomer forms of the polyamino acids are particularly preferred. The d-isomer forms can not be readily degraded in most living tissues, however the d-isomer forms can be degraded by the liver and kidney, where d-proteases are present. One of skill in the art should readily appreciate that the polyamino acid polymer or copolymer carriers may have various amino acid substitutions, so long as such substitutions do not have a deleterious effect on the carrier properties of the polyamino acid polymer or copolymer. Such substitutions are therefore considered to be within the scope of the invention.

Examples of other suitable carriers for the chelating agent-paramagnetic metal complex include macromolecules, emulsions, liposomes, and microspheres, which are of a size typically less than 5 microns in diameter to avoid entrapment within (and possible adverse effects to) the lungs. Further examples of alternative or substitute carriers for the chelating agent-paramagnetic metal ion complex are described in U.S. Patent No. 5,213,788, which is incorporated herein by reference. Another suitable protein carrier is cholera toxoid. The length of the carrier may range from about 50 to about 200 residues, more preferably about 100 residues. The molecular weight (MW) may range from about 15,000 to about 60,000, preferably from about 15,000 to about 30,000.

The chelating agents for conjugation with the carrier molecule, and complexing with the paramagnetic atom can be selected from the non-toxic group of chelating agents of polyaminopolycarboxylic acids as described in Chapter 14 of Stark and Bradley. Particularly suitable chelating agents for practicing the present invention are DOTA and DTPA. Examples of other suitable alternative chelating agents are as follows: Aquo iron, EDTA, DTPA-BMA, BOPTA, TTHA, NOTA, D03A, HP-D03A, TETA, HAM, DPDP, Acetate, TPPS ₄ , EHPG, HBED, and Desferrioxamine B. Additional chelating agent

derivatives which may be substituted in the present invention are described in U.S. Patent No. 5,281,704, which is incorporated herein by reference.

With regards to paramagnetic species, any atom having paramagnetic properties is considered suitable in the practice of the invention. This includes transition elements of atomic numbers 21-29, 42 or 44 and elements of the Lanthanide series. These transition metals include Cr ^*3 , Cr ^*2 , Mn* ³ , Mn ^* ,Fe ^*3 Fe ^*2 , Cu ^*2 , Co ^*3 , Co ^*2 , Ni ^*2 and radioisotopes thereof. Preferred are members of the Lanthanide series which are numbered 59-70. This encompasses Pr, Nd, Pm, Sm, Eu, Gd, Tb, Dy, Ho, Er, Tm, and Yb, and the respective radioisotopes thereof. More particularly preferred is the Lanthanide element gadolinium (Gd) . Gadolinium is particularly suitable as the paramagnetic metal of the contrast agents of the present invention as it has a large magnetic moment, which efficiently relaxes magnetic nuclei. Gadolinium's strong paramagnetic properties are the result of its seven unpaired electrons. The unexpectedly highly concentrated gadolinium incorporated in the contrast agents of the present invention readily passes through the body and is safely excreted without causing toxic side effects. Other examples of alternative paramagnetic species are disclosed in U.S. Patent No. 5,213,788 which is incorporated herein by reference. Another advantageous aspect of the contrast agents of the present invention is an embodiment which is the conjugation of the contrast agents with various macromolecules, which macromolecules have the capability of targeting a tissue or organ. The contrast agents of the present invention can be coupled as conjugates with such macromolecules that are known to target an organ or part of an organ to be examined. Particularly desirable or interesting macromolecules are those which are capable of targeting specific sites, e.g., cellular receptors or antigens. This favorably provides for target- specific contrast agents.

These target-specific macromolecules include, but are not limited to, hormones such as insulin, prostaglandins, steroid hormones, amino sugars, peptides, proteins, e.g., serum

albumins, lipids, and polysaccharides. Antibodies, such as polyclonal or, more particularly, monoclonal, are especially suitable for conjugation with the contrast agents of the invention for targeting specific sites of interest. Particularly interesting examples of monoclonals are those which are specific to tumor-associated antigens, or which exhibit a desired diagnostic specificity, e.g., antimyosin. These contrast agents of the present invention provide a further battery of useful tools for diagnostic image analysis. Non- limiting examples of tumor-specific monoclonals would include: breast, lung, and prostate cancers. Other suitable monoclonal antibodies may be directed to non-tumor antigens, for example, Alzheimer's marker antigens, which may advantageously provide for earlier clinical diagnosis and pharmaceutical intervention to ameliorate the disease.

The present invention advantageously and unexpectedly provides target-specific contrast agents, which maintain their target specificity in vivo . Such conjugated target-specific contrast agents of the present invention advantageously allow for selection of appropriate biodistribution characteristics. These conjugates permit tissue or organ targeting, i.e., preferential delivery to such tissue material as, e.g., tumors. This in turn provides for improved imaging characteristics, e.g., contrast, better selectivity, contrast/noise ratio, imaging time, enhanced signal intensity, and the like, for imaging such targets of interest.

METHOD OF SYNTHESIS

A method of making or synthesizing the contrast agents of the present invention is carried out as described hereinafter. The method of the invention provides for a preparation of stable and non-toxic contrast agents, which method of synthesis is simpler and more efficient than other currently available techniques. The method uses commercially available reagents. The method also advantageously provides flexibility in the production of small or large quantities of the contrast agents of the invention for administration, depending upon the size of the subject mammal. Suitable and

preferred materials or substituents for the contrast agents of the present invention have been described above.

For the synthetic method, an appropriate chelating agent and conjugating agent can be dissolved in an aqueous solution, which solution is suitable for maintaining the linear structure of the carrier to be added. Preferred is a saturated urea solution. The volume of the aqueous solution may range from about 200 microliters to about 20 ml. Any conjugating agent is suitable. Preferred conjugating agents are EDAC or glutaraldehyde. An appropriate base can be added by any appropriate means to the solution and in an amount sufficient to assure complete dissolution of the chelating agent.

The amounts of chelating agent may range from about 9 to 900 mg. The amount of conjugating agent may range from about 20 μmol. to about 2 mmol, and may vary depending on the amount of contrast agent desired.

A suitable amount of carrier is then added to the solution for conjugation with the chelating agent. This amount may range from about 2 mg to about 200 mg. pH is maintained at less than about 5 by addition of any suitable acid. After about one hour, a sufficient amount of water may be added to the solution. The solution is then incubated for a suitable period of time sufficient to allow for complete conjugation of the carrier and complexing agent. For example, the solution may be typically incubated for a period of about 12 hours at a temperature of about 4°C.

Following incubation, the solution is warmed to approximately room temperature. A suitable paramagnetic metal salt is then added to the solution. For example, gadolinium chloride hexahydrate (Gd C1 ₃ -6H ₂ 0) may be added. A suitable amount of the paramagnetic salt may range from about 10 mg to about 1 g. The pH of the reaction is maintained above about 7 by way of addition of an appropriate base. After a time sufficient to allow for complete conjugate formation of the carrier-chelating agent - paramagnetic metal complex, the solution may be dialyzed. At least about 5 hours is typical to allow for complete conjugation. Dialysis is carried out with an appropriate chelating agent for a time sufficient for removing

any excess paramagnetic metal. Generally suitable is dialysis with EDTA for about 24 hours. The dialysis may be carried out by any method known to those skilled in the art. The solution containing the contrast agent of the present invention may then be dialyzed against water for a period of time sufficient for de-salting. This is typically for about 24 hours. Other known de-salting techniques may be employed such as gel-filtration. The solution may then be stored in liquid or lyophilized form, if desired, for later use. If one desires to analyze with the aid of fluorescence, a suitable fluorescing agent may be added along with the addition of the paramagnetic metal. Typically, the molar ratio of paramagnetic metal to fluorescing agent ranges from about 2:1. An example of a suitable fluorescing agent is TbCl ₃ .

The degree of conjugation of carrier and chelating agent after the first conjugation reaction of the method of the invention is typically less than about 35%. This value is independent of an excess of chelating reagent: a double excess of, for example, DOTA is required due to the possibility of its precipitation at low pH. The degree of conjugation has been noted to decrease with higher pH. While wishing not to be limited or bound by any particular theory, the relatively low efficiency of the first conjugation may be due to the interaction between conjugated chelating agent and carrier. For the complexing agent, DOTA, it has a pK ₃ =9.73 (Stetter, 1976) . These values can further decrease for the conjugated molecule, which has a modified carboxyl. This probably means that two carboxyls of DOTA have a negative charge at a pH of about 5. At the same time, most of the amino groups of the polyaminoacid carrier, such as polylysine, are charged positively. As a result of electrostatic interaction, every conjugated molecule of DOTA is able to block at least two unbound amino groups of polylysine preventing their further participation in the reaction. Complexing with Gd ^3* compensates for the negative charges of DOTA. This favorably releases amino groups foi further conjugation, if desired by one of skill in

the art, to advantageously increase the efficiency of conjugation of the method of the invention.

The method of the invention advantageously provides a second conjugation step for increasing the efficiency of conjugation, which utilizes and subjects the conjugate synthesized in the first conjugation with all the steps described above. In the second conjugation, the conjugate replaces the carrier used in the first conjugation. The second conjugation reaction unexpectedly and advantageously results in an increased concentration of paramagnetic atom bound to the conjugate. Following the second conjugation, the concentration of paramagnetic atom shows an increased efficiency of conjugation in a range from about 50 to about 55%. The increased concentration of bound paramagnetic atom (and hence increase in efficiency of conjugation) is demonstrated by comparing relaxation times for the respective conjugations. The first conjugation reaction shows that the relaxation time, T ₁₍ is equal to 0.15 seconds. The value of Tj for the second conjugation is advantageously and unexpectedly shortened to 0.08 seconds for a 1.5 ml solution, which is equal to 3 and 5 μmol Gd. DOTA, respectively, for relaxivity of Gd. DOTA (3.4 mM^ε ^"1 ) .

The increased concentration of bound paramagnetic atom has been quantitated to advantageously and unexpectedly represent a number ranging between about 150 to 200 atoms. This is a concentration not heretofore reported.

The amount or yield of contrast agent synthesized by way of the present invention typically ranges from about 2 mg to about 200 mg of product, depending on the amount of reactants utilized. The contrast agents of the invention may be further advantageously protected from bi©degradation, which otherwise may occur during in vivo use. Any treatment with which one of skill in the art is familiar may be suitable, so long as the treatment does not disrupt the integrity of the complex. Preferred is acetylation. Other examples are treatment with succinic or propionic anhydride.

The contrast enhancing agents of the present invention are readily usable in any detection or imaging system involving

administration of paramagnetic marker or tracer ions. The appropriate paramagnetic metal may be added to the carrier- chelate complex at a suitable pH consistent with stable chelation bindings. Another embodiment of the present invention provides method for producing target-specific contrast agents for imaging, particularly for, but not limited exclusively to MRI applications. These contrast agents of the present invention are suitable for use both as diagnostic pharmaceuticals in clinical medicine and as biologic probes. Target-specific contrast agents are particularly useful, because they aid the medical practitioner in locating specific tissues or organs of interest in a patient for detection of abnormal or diseased tissue. The specificity of location is provided by the contras agents' specific bonding to the tissue or organ to be examined. The tissue of interest to be examined is thus bound by the target-specific contrast agents of the present invention. The target tissue, when diseased, effectively contrasts with the normal surrounding tissues during an imaging procedure. The target-specific contrast agents of the invention having enhanced conspicuity or signal intensity advantageously provide a visually-enhanced image of a particular tissue of interest. The advantages of such are readily apparent.

With regards to synthesizing target-specific contrast agents, any macromolecule having target-specific capability is considered suitable for conjugation with the contrast agents of the present invention.

Any protein, or peptide fragments thereof, is suitable for linking or conjugating to the contrast agents of the invention for the purpose of targeting a specific tissue. Non- limiting examples of such suitable targeting proteins are hormones, antibodies, polyclonal or particularly monoclonal, or the Fab fragments thereof, and lectins, such as wheat germ agglutinin. For example, a contrast agent-antibody combination may be used to locate specific diseased tissues, such as breast, lung, brain, and prostate tumors, which possess antigenic determinants specific to the antibody conjugated to the contrast agents of the invention. Alternatively, non-tumor sites of

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interest may also be targeted by way of a suitable antibody, e.g., a marker antibody for Alzheimer's.

The contrast agent-wheat germ agglutinin combination may be advantageously used as a means to locate and target particular neural connections of interest within the mammalian brain as a means of brain mapping.

Other macromolecules which are suitable for targeting include prostaglandins, amino sugars, polysaccharides and lipids. Hence, these macromolecules may also be utilized in the synthesis of the target-specific contrast agents of the present invention.

With regards to synthesizing the target-specific contrast agents of the present invention, the method provides for the conjugation of the macromolecule with the contrast agent of the invention. For example, the contrast agent may be provided in a suitable salt solution. The macromolecule can then be added to the solution along with an appropriate conjugating agent. The reactants are incubated for a period of time sufficient for conjugation of the macromolecule with the contrast agent. Typically, a period of about 24 hours, in which the target-specific conjugate is maintained at a temperature of about 4°C, is suitable. The target-specific contrast agent can then be separated from excess conjugating agent by any appropriate method known to one of skill in the art. One suitable method is gel filtration. Other methods are readily known to one of skill in the art. The contrast agents can be stored as described as above.

We have demonstrated that advantageously and unexpectedly between about 150 to 200 paramagnetic ions are attached per macromolecule of the conjugate. This is a greater number of attached or bound paramagnetic ions than has heretofore been reported.

METHODS OF ADMINISTRATION

Another aspect of the present invention is directed to a method for clinical or diagnostic analysis by administering the contrast agents of the present invention to a host, preferably a mammalian host, in an amount sufficient to effect

the desired enhanced contrast (or shift) . The host may then be subjected to diagnostic analysis. Preferably, diagnostic analysis is MRI or NMR imaging analysis. Further, the contrast agents are useful in x-ray image or ultrasonic analysis. While described primarily as contrast enhancing agents, the contrast agents of the invention may also act as NMR shift reagents, and such use is contemplated to be within the scope of the invention.

A detailed discussion of the theoretical considerations in selecting the appropriate parameters for MRI and NMR diagnostic analysis is disclosed in U.S. Patent No. 4,749,560 which is incorporated herein by reference. CAT scans, x-ray image analysis and ultrasonic diagnosis are carried out in accordance with well-established techniques. The contrast agents of the invention may be administered to a mammal, including a human patient, in the form of a pharmaceutical composition in a contrast-, or visually- enhancing amount, together with a pharmaceutically acceptable carrier. The contrast enhancing agents of the invention are administered in an amount clinically or diagnostically sufficient to effect the desired enhanced contrast. For MRI, this amount is an MRI signal-affecting amount, i.e., an amount that will alter the spin-lattice, spin-spin or spin-echo relaxation times of an MRI signal. This alteration is affected so as to enhance the signals received from the patient under analysis by reducing the aforementioned relaxation times with respect to an area of the patient.

In another embodiment, the MRI signal affecting amount is that amount, which in addition to altering the relaxation times of the MRI signals in the patient, will also advantageously sufficiently alter such relaxation times, so that the desired level of differentiation can be achieved. This provides a visually-enhanced differentiation between those parts of the patient that have and have not taken up the contrast agents of the present invention.

The enhanced visualization of an image by way of the present invention favorably results from the increased concentration of bound paramagnetic atom, as described above. With regards to administration, the compositions of the present invention are administered in doses effective to achieve the desired enhancement or improved contrast. Such doses may vary, depending upon the particular paramagnetic ion complex employed, the organs or tissues targeted, MRI equipment and the like. Effective amounts typically may range from about 5 to about 500 micromoles of the paramagnetic ion complex per liter. The doses administered orally or parenterally may range from about 1 to about 100 micromoles per kilogram of body weight, which corresponds to about 1 to about 20 mmol for an adult human patient. For smaller patients or animals, the dosage may be varied accordingly.

The particular paramagnetic atom employed and organ to be imaged will determine the waiting period between administration and imaging. It will generally be at least about 15 minutes but typically less than about an hour. Compositions are provided having effective dosages of contrast agents in the range of about 0.001-5mmol per kg for NMR diagnostics, preferably about 0.005-0.5mmol per kg; in the range of about 0.1-5mmol per kg for x-ray diagnostics; and in the range of about 0.1-5mmol per kg for ultrasound diagnostics. The compositions of the present invention can be administered by any number of well-known routes. These include intravenous, intraarterial, intrathecal, intraperitoneal, parenteral, enteral, oral, intrapleural, subcutaneous, by infusion through a catheter, or by direct intralesional injection.

While one of skill in the art may readily ascertain an effective route of administration of the contrast agents of the invention, the following guidelines are provided. Intravenous, intraarterial or intrapleural administration is generally suitable for use for lung, breast, and leukemic tumors.

Intraperitoneal administration is suitable for ovarian tumors. Intrathecal administration is suitable for brain tumors. Subcutaneous administration is suitable for Hodgkins disease,

lymphoma and breast carcinoma. Catheter infusion is useful for metastatic lung, breast or germ cell carcinomas of the liver. Intralesional administration is useful for lung and breast lesions. Depending on the route of administration, the pharmaceutical compositions may require protective coatings, which are known in the art.

For parenteral administration, the compositions may be injected directly or mixed with a volume of carrier sufficient for systemic administration. Formulations for enteral administration may vary widely, as is well-known in the art. In general, such formulations include an effective amount of the contrast agent of the invention in aqueous solution or suspension. Such enteral compositions may optionally include buffers, surfactants, thixotropic agents, and the like. Compositions for oral administration may also contain flavoring agents and other ingredients for enhancing their organoleptic qualities.

The pharmaceutical compositions of the present invention containing the contrast agents of the present invention, which contrast agents are essentially neutral, may be provided for injectable use in sterile solutions or dispersions, or in sterile powders for the extemporaneous preparation of sterile injectable solutions or dispersions. The composition is preferably sterile and fluid. Sterilization can be achieved by any art recognized technique, including but not limited to, addition of antibacterial or antifungal preservatives, for example, paraben, chlorobutanol, phenol, sorbic acid, thimerosal, and the like, so long as the integrity of the contrast agent of the composition is not adversely affected. Further, isotonic agents, such as sugars or sodium chloridemaybe incorporated into the present composit

Production of sterile injectable solutions containing the contrast agents of the present invention is accomplished by incorporating the contrast agents in an appropriate solvent with various ingredients enumerated above. Sterilization may then be carried out, for example, by filter sterilization. To obtain a sterile powder, the above solutions may be vacuum-, or freeze-dried as necessary.

The contrast agents of the invention are thus compounded for convenient and effective administration in pharmaceutically effective amounts with a suitable pharmaceutically acceptable carrier in a dosage form, which composition favorably affects contrast enhancement or conspicuity in a manner which heretofore has not been accomplished.

As used herein, a pharmaceutically acceptable carrier includes any and all solvents, dispersion media, coatings, preservatives, antibacterial and antifungal agents, isotonic agents, and the like. The use of such materials is well-known in the art.

Typical pharmaceutically acceptable carriers are well- known and include a solvent or dispersion medium containing, for example, water, buffered aqueous solutions (i.e., biocompatible buffers), ethanol, polyol (glycerol, propylene glycol, polyethylene glycol and the like), suitable mixtures thereof, surfactants or vegetable oils.

KIT Another embodiment of the invention is a kit containing the contrast agents of the present invention suitable for commercial sale.

With regards to the kit, a solution of the contrast agents may be sterilized and made up into containers of ampules or vials, or may be lyophilized to a powder for dissolution when ready to be used. The contrast agents may be mixed with a carrier, as discussed above. If the contrast agent is provided in lyophilized form, the carrier may also be provided in appropriate vials or ampules for mixing with the lyophilized powder. If desired, ampules may contain lyophilized powder of the contrast agent in one compartment and a carrier in another, the compartments being separated by a frangible barrier. When ready to use, the barrier is broken and the ampule is shaken to form a solution suitable for administration. Prior to administration of the contrast agent of the present invention, the reconstituted contrast agent may be further diluted by addition of a suitable diluent such as:

Ringers Injection, USP

Sodium Chloride Injection, USP

Dextrose Injection, USP (5% dextrose in sterile water) Dextrose Sodium Chloride Injection, USP (5% dextrose in sodium chloride)

Lactated Ringers Injection, USP

Protein Hydrolysate Injection Low Sodium, USP

Water for Injection, USP, preferably of a suitable osmolality.

The amounts of the contrast agents in solution or lyophilized powder form may be provided in any suitable amount for commercial use in the appropriate clinical setting.

Alternatively, reagents for making the contrast agents of the invention may be provided in separate ampules or vials for the purpose of the buyer or user synthesizing the contrast agent by way of the present invention, if so desired.

ALTERNATIVE METHODOLOGIES

It is contemplated that the contrast agents of the present application can be employed in a wide variety of applications.

Recent advances in MRI and related technologies have resulted in new and potential applications of the contrast agents of the present invention. The development of superconducting quantum interference devices (SQUIDS) has led to exceedingly sensitive detectors of magnetic fields which can be utilized to measure relaxation phenomena, as described in Scientific American, August, 1994, which is incorporated herein by reference. The sensitivity of SQUIDS in detecting changes in magnetic flux is 100 times more sensitive than the amount of mechanical energy to raise a single electron one millimeter in the earth's gravitational field or 10" ³² Joules. These devices approach the quantum fundamental boundaries as set by Heisenberg's uncertainty principle. SQUID systems are increasingly being utilized for biomedical applications. Thus,

the contrast agents of the present invention may play a role in this evolving technology.

The contrast agents of the present invention can also be utilized in conjunction with other types of imaging technology including, but not limited to, x-ray, ultrasound and acoustic imaging. In particular, the radioactive metal species and complexes of the contrast agents of the invention can be utilized as diagnostic, monitoring and therapeutic agents. With regards to particularly interesting medical applications, the contrast agents of the invention can be utilized in a variety of radiographic procedures including, but not limited to, those involving cardiography, coronary arteriography, aortography, cerebral and peripheral angiography, arthrography, intravenous pyelography and urography. In addition, the contrast agents can be advantageously utilized as carriers to deliver pharmaceuticals, including radiopharmaceuticals, to various body sites with or without target specificity. The advantage of this technique is that drug delivery can be monitored in real time with specificity to the organ system or tissue under examination. Furthermore, the pharmaceutic can be targeted to a given site (e.g., a tumor or site of infection) and/or release its therapeutic agent at the target site.

Contrast agent utilization is not limited to medical applications. As magnetic resonance and other imaging and monitoring technologies proliferate, more industrial applications are evolving. For example, magnetic resonance technology has been applied to oil exploration. The advent of SQUIDS has made it possible to map the earth's crust to determine the whereabouts of oil or geothermal energy sources. In this context, contrast agents can be utilized to map, track, and monitor oil deposits and their flow rates. In addition, contrast agents can be used to diagnose flow rate and/or leaks in oil pipeline delivery systems. Other types of industrial usage include monitoring and feedback systems in production or manufacturing processes as disclosed in U.S. patent 5,015,954, herein incorporated by reference. The contrast agents of the present invention can be

applied to such processes to assist in the means of monitoring, analysis and quality control.

ADVANTAGES

The present invention represents a significant improvement in the state of the art with regards to contrast agents and method of synthesis of the agents. Conjugating antibodies with gadolinium has been known for several years, but the present method of conjugation produces a more clinically and commercially useful contrast agent. The method of the invention provides contrast agents having a greater concentration of bound paramagnetic atom than heretofore accomplished. This advantageously and unexpectedly provides for enhanced signal intensity or conspicuity. The contrast agents of the invention thus provide a superior MRI contrast, as compared with other contrast agents.

Further in this regard, the present invention advantageously provides contrast agents having a significantly higher concentration of a paramagnetic metal, such as gadolinium, conjugated to a targeting molecule than has heretofore been achieved. The heavier-loaded targeting molecule surprisingly better retains its biological activity than in other reported methods.

The contrast agents of the present invention unexpectedly provide for shorter imaging time at a given level of point resolution. Shorter imaging times are achieved because of the greater signal enhancement and image contrast produced per unit utilized of the contrast agents of the present invention.

The method of the present invention for making the contrast agents is also advantageously and unexpectedly simpler and easier than other reported methods.

Given the tremendous growth in the diffusion of clinical MRI technology over the past decade, and the current healthcare environment with concerns over cost and duplication of diagnostic tests, the present invention advantageously represents a significant potential for combining the

technological strengths of MRI with target-specific imaging techniques, such as nuclear medicine.

While the preferred aspects and embodiments of the invention have been described in detail above to allow one of skill in the art to carry out the invention, it should be appreciated that various substitutions may be made, if one of skill in the art is satisfied with less than preferred or optimal contrast agents.

The invention is further illustrated by the following examples, which should not be construed in any fashion as limiting the spirit or scope of the invention.

EXAMPLE 1

PREPARATION OF PL-Gd-DOTA BY TWO-STEP CARBODIIMIDE CONJUGATION

In a typical preparation 9 mg of DOTA (22 umol) and 3.84 mg of EDAC (20 V-mol) are dissolved in 200 μL of saturated urea solution. Addition of IN NaOH can be added to assure complete dissolving of the DOTA, 2.1 mg of polylysine PL (10 v-mol lysine, 100 nmol PL) is added. pH is maintained less at than 5 by IN HC1. After 1 hr, 200 uL water is added and then the solution is incubated 12 hrs at 4>c.

The solution is warmed to room temperature and 10 mg of GdCl ₃ -6H ₂ 0 (27 ymol) is added; pH is maintained above 7.0 by IN NaOH. If experiments include analysis of fluorescence, an equivalent quantity of GdCl ₃ and TbCl ₃ mixture with molar ratio 2:1 is used. After 5 hrs., the solution is dialyzed (MWCO 12,000-14,000) 24 hrs against 8 mM trisodium EDTA and 24 hrs against water and lyophilized. The yield of PL-Gd-DOTA after lyophilization is typically 2.2-2.5 mg.

In the second step of conjugation all the procedures are performed in the same way using prepared PL-Gd'DOTA instead of PL. Another chelating agent, DTPA, may be used in the reaction instead of DOTA. In this case, all the operations and quantities of reagents are the same as in the first conjugation.

EXAMPLE 2 PROTECTION OF PL-Gd-DOTA FROM BIODEGRADATION

Dissociation of conjugated polylysine within the cells creates a serious problem for in vivo use. There are several mechanisms by which cells may degrade exogenous proteins. The most important is binding of ubiquitin to the amino group of lysine with the further removal of bound amino acid from the protein chain. This process can be prevented by acetylation of

residual amino groups of PL-Gd-DOTA making binding between them and ubiquitin impossible.

After the second step of conjugation, an equal volume of saturated sodium acetate is added to the dialyzed solution. The mixture is cooled on ice and 30 yL of acetic anhydride is added in 5 uL portions at 30 minute intervals. The pH is checked before each addition and maintained at 9 by IN NaOH to prevent the dissociation of Gd-DOTA in acid media. The solution is then incubated for 12 hrs at 4oc and desalted by dialysis and gel-filtration (Sephadex G-25, water).

Acetylation insures protection of the polymer from rapid destruction by ubiquitin. In order to protect the contrast agent over longer periods of time from protease degradation, poly-d-lysine (or poly-d-ornithine) instead of biological 1-isomer is used. This polymer cannot be easily degraded in most living tissues, however it can be utilized by the liver and kidney, where d-proteases are present.

EXAMPLE 3

CONJUGATION OF PL-Gd-DOTA WITH PROTEINS Essentially desalted PL-Gd-DOTA solution is lyophilized and dissolved in 100 yL of 10 mM KH ₂ P0 ₄ followed by the addition of 1 mg of EDAC and 0.5 mg of WGA (12 nmol) . After 24 hrs at 4<C, the conjugate is separated from excess of glutaraldehyde by gel-filtration (Sephadex G-50, water) . The MRI-analysis shows that 150-200 Gd atoms (or 3-4 polymer chains) are attached to 1 molecule of WGA. According to Wright (1984), WGA has a dimer structure; each monomer has 6 lysine residues, which are probably involved in the conjugation with carboxyl groups of PL-DOTA complex. Prepared contrast agent is used for direct MRI investigation of axonal transport in the cat brain and (with addition 30% TbCl ₃ ) for its fluorescence visualization.

EXAMPLE 4

CONJUGATION OF PL-Gd-DOTA WITH ANTIBODY

The same method of conjugation is used for preparation of the MRI contrast agent with monoclonal IgGl anti-vitamin B ₁₂ antibody (Sigma, #V9505, clone #CD-29) . Antibody solution is dialyzed against water and 30 uL (5 nmol of protein) is conjugated with PL-Gd-DOTA obtained from 1 mg of PL. Antigen is then added and the mixture is gel-filtered through Sephadex G-200 with elution by water. The first elution peak with absorption at 280 nm has also 360 nm and 548 nm absorption of vitamin B ₁₂ , which means the presence of the antibody-antigen complex. This peak is separated from the major peaks of excessive polylysine and antigen. Eluted solution of antibody- antigen complex has a concentration of antibody of 0.6 uM, antigen of 1.7 uM (measured spectrometrically) and Gd-DOTA 130 uM (measured by MRI; Tjsl.δs). This means that up to 200 Gd

- 31 -

atoms are conjugated to antibody without loss of its ability to bind antigen.

EXAMPLE 5

CONJUGATION WITH GLUTARALDEHYDE If conditions of carbodiimide reaction are not suitable for protein survivability, conjugation with PL-Gd-DOTA can be provided by glutaraldehyde. A molecule of acetylated polymer still has several free amino groups, which are able to react with glutaraldehyde. In a typical preparation, a solution of PL-Gd-DOTA in 300 yL lOOmM phosphate buffer (pH=7) is added in 30 yL portion to ice-cooled 200 yL 2% glutaraldehyde. After 12 hrs, the incubation mixture is gel-filtered (Sephadex-25, PBS) . The fraction with absorption at 280 nm is collected and added to the protein solution. The mixture is incubated 24 hrs at 4©C and gel-filtered through the gel, which is suitable for used protein. This method of conjugation has an efficiency comparable to carbodiimide reaction and is suitable for preparation of the MRI contrast agents conjugated with antibodies and other macromolecules. EXAMPLE 6

IN VITRO TESTING FOR CONTRAST CONSPICUITY AND RELAXIVITY

Adequate potential for signal enhancement was confirmed by examining vials filled with sample solutions in a 1.5 Tesla clinical MR imaging machine (Signa Systems, GE, Milwaukee, USA) . Qualitative evaluation of signal intensity relative to water vials and gel phantoms was performed as was a more rigorous quantitative evaluation. For quantitative measurement, multiple imaging sessions were performed using a linear extremity coil with varying TR for a fixed TE value with other parameters held constant. The signal intensity was measured by two observers in consensus fashion at the imaging system console using a region of interest cursor. This was performed for each vial after each TR increment. The TR was varied from 1600 ms to less than 100 s and the signal intensity alteration was plotted versus the repetition time in order to enable a calculation of the approximate Tj relaxation rate constant. Figure 1 shows a sample image from a T _: relaxation experiment.

EXAMPLE 7

ADMINISTRATION OF CONTRAST AGENT CONJUGATED WITH WHEAT GERM AGGLUTININ (WGA)

Using a stereotaxic frame, an anesthetized cat was maintained in the Horsley-Clark plane. Under aseptic conditions and in compliance with all Federal, University and local regulations a craniotomy was performed. The visual cortex was exposed and a Hamilton 30 gauge microliter syringe was preloaded with the contrast agent containing gadolinium conjugated with WGA for injection. This was guided to 2 mm below the cortical

surface and 0.2-0.4 microliter amounts of the conjugate at a concentration of 20 mg/ml was injected with greater than 1 millimeter of surface separation. The craniotomy was closed after the injections were completed and the animal was allowed to recover. Axonal tracing was carried out as shown in Figures 3 and 4. Fluorescence microscopy was carried out using TbCl ₃ to confirm the presence of the contrast agent, as shown in Figure 5.

EXAMPLE 8 ADMINISTRATION OF CONTRAST AGENT CONJUGATED

WITH ANTIBODY TO ANTIGEN 301

Using a stereotaxic frame, the anesthetized cat was maintained in the Horsley-Clark plane. Under aseptic conditions and in compliance with all Federal, University and local regulations a craniotomy was performed. The visual cortex was exposed and a 25 gauge 3.5 inch needle was mounted vertically in a stereotactic carrier. Using an atlas for guidance, the ventricle was entered and a small quantify of CSF-approximately the same volume as the injectate-was removed. The material (0.33 ml) of cat 301 conjugated with the gadolinium contrast agent of the present invention at a concentration of 3 mg/ml was then infused into the left ventricle and the craniotomy was closed. Figure 2 shows a coronal image of the contrast agent, conjugated with antibody directed to antigen 301, (white material shown by arrows) localized in the cat brain at the site of the 301 antigen. This demonstrates that antibody conjugated with the contrast agent of the present invention advantageously retains its ability to bind in vivo its target antigen.

It is to be understood that the foregoing detailed description and accompanying examples are merely illustrative and are not to be taken as limitations upon the scope of the invention, which is defined solely by the appended claims and their equivalents. Various changes and modifications, including without limitation those relating to the substituents, derivatives, syntheses, formulations and/or methods of use of the invention, may be made without departing from the spirit and scope thereof.

PUBLICATIONS

LITERATURE:

Desreux J.F. (1980) . Nuclear magnetic spectroscopy of lanthanide complexes with tetraaza macrocycle. Unusual conformation properties. Inorg. Chem. , 19, 1319-1324.

Sieving P.F. Watson A.D. and Rocklage S.M. (1990). Preparation and characterization of paramagnetic polychelates and their protein conjugates. Bioconjugate Chem. , 1(1), 65-71. Stetter H. and Wolfram F. (1976) . Complex formation with tetraazacycloalcane-N,N' ,N",N" '-tetraacetic acids as a function of ring size. Angew. Chem. , Int. Ed. Engl., 15(11), 686. Wright C.S., Gavilanes F. and Peterson D.L. (1984). Primary structure of wheat germ agglutinin isolectin 2. Peptide order deduced from X-ray structure. Biochemistry, 23, 280-287. Clarke J. (August, 1994) SQUIDS Scientific American , pages 46- 53. All publications are incorporated herein by reference.