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(CANCER RESEARCH 52, 4396-4401, August 15, 1992] Disposition Characteristics of Macromolecules in the Perfused Tissue-isolated Tumor Preparation1 Hirofumi limito, Yumi Sakamura, Kazuhiro Ohkouchi, Ryo Atsumi, Yoshinobu Takakura, Hitoshi Sezaki, and Mitsuru Hashida2 Department of Basic Pharmaceutics, Faculty of Pharmaceutical Sciences, Kyoto University, Sakyo-ku, Kyoto 606, Japan ABSTRACT Disposition characteristics of model macromolecules with different physicochemical characteristics and macromolecular prodrugs of mitomycin ( . namely mitomycin C-dextran conjugates, were studied in tis sue-isolated tumor preparations of Walker 256 carcinoma with the use of a single-pass vascular perfusion technique. In constant infusion ex periments, all radiolabeled macromolecules accumulated in the tumor tissue, but the degree and pattern of distribution greatly varied, depend ing on their electric charges. Positively charged macromolecules were markedly accumulated compared with those that were neutral or nega tively charged. In addition, their concentrations were significantly higher in viable than in necrotic regions, while neutral and negative compounds were distributed in necrotic rather than in viable regions. Pharmacokinetic analysis of tissue concentration-time courses of posi tively charged diethylaminoethyl and neutral dextrans showed that their movement occurred by convective fluid flow, and that high tissue accu mulation of positively charged macromolecules could be explained by strong binding due to electrostatic interaction. For neutral and anionic macromolecules with negligible affinity to the tissue, it was suggested that the final concentration gradient between the viable and necrotic regions was decided by their tissue fluid content. Thus, the present study revealed the basic disposition characteristics of macromolecules in tu mor tissue relative to their physicochemical properties. INTRODUCTION In cancer chemotherapy, it is important to deliver antitumor drugs selectively to the tumor with minimum exposure of other normal tissues, and various drug carrier systems have been de veloped for achieving this. Conjugation of antitumor drugs to macromolecules seems to be one of the most promising ap proaches, since diverse physicochemical properties and func tions of macromolecules can be utilized for control of drug disposition (1-3). In a series of investigations, we developed macromolecular prodrugs of MMC,3 which are MMC-dextran conjugates hav ing cationic and anionic charges as well as a variety of molec ular weights, and examined their physicochemical, pharmacokinetic, and pharmacological characteristics (4-11). The disposition and subsequent pharmacological effects can be con trolled by selecting specific physicochemical properties. Tumor targeting in vivo was achieved by systemic injection of MMCDan in mice (10). These results were explained by the Received 12/10/91; accepted 6/8/92. The costs of publication of this article were defrayed in part by the payment of page charges. This article must therefore be hereby marked advertisement in accord ance with 18 U.S.C. Section 1734 solely to indicate this fact. 1 Supported in part by a Grant-in-Aid for Scientific Research from the Ministry of Education, Science and Culture, Japan. 2 To whom requests for reprints should be addressed. 3 The abbreviations used are: MMC, mitomycin C; MMCD, mitomycin C-dex tran conjugate; MMCDo,,, cationic mitomycin C-dextran conjugate; MMCD„, anionic mitomycin C-dextran conjugate; DEAED, diethylaminoethyl dextran; CMD, carboxymethyl dextran; BSA, bovine serum albumin; cBSA, cationized bo vine serum albumin; EB/BSA, bovine serum albumin labeled with Evan's blue; VRS, vascular reference substance; T-10. T-70, dextrans with molecular weights of 10,000 and 70,000. general relationships between the physicochemical characteris tics and in vivo behavior, including tumor localization, which we established for various model macromolecules (12). We fur ther developed a monoclonal antibody-MMC conjugate by us ing MMCDan as an intermediate. Immunotargeting was achieved, based upon these findings (13). On the other hand, we established an experimental system for the evaluation of the drug disposition in the tumor at the organ level by using a tissue-isolated tumor preparation and moment analysis (14). This system was applied to the pharmacokinetic analysis of the disposition of antitumor drugs, including MMC and its lipophilic prodrugs. The present study aimed to clarify the disposition characteristics of model macromolecules and MMCD in tumor tissue with the use of this system and to construct a strategy of tumor targeting with a macromolecular drug carrier system. MATERIALS AND METHODS Chemicals. MMC was kindly supplied by Kyowa Hakko Kogyo Co., Tokyo, Japan. Dextrans were purchased from Pharmacia Fine Chem icals Co., Uppsala, Sweden, and had average molecular weights of about 10,000 (T-10) and 70,000 (T-70). BSA (Fraction V) was obtained from Armour Pharmaceutical Co., United Kingdom. The sources of radiochemicals were as follows: 7-amino[t/-14C]butyric acid (74 MBq/mg); [i/-'4C]sucrose (0.11 MBq/mmol); and [methoxy-^Cfinulm (0.35 MBq/g), New England Nuclear, Boston, MA; potassium [l4C]cyanide (29.5 MBq), Amersham Japan, Tokyo; indium chloride ('" In Cla), Nihon Mediphysics, Takarazuka, Japan. All other chemicals were of reagent grade, obtained commercially. Preparation of Model Macromolecules. DEAED(T-70) and CMD(T-70) were synthesized by reacting (diethylamino)ethyl chloride hydrochloride and monochloroacetic acid with dextran(T-70) in alkaline solutions, respectively (12). Radiolabeled DEAED(T-70) and CMD(T-70) were synthesized by using [carooArv-l4C]dextran(T-70). Both [carooxy-l4C]dextran(T-10) and [carftojcy-14C]dextran(T-70) were pre pared by reacting potassium [l4C]cyanide with dextrans according to the method of Isbell et al. (15), as reported previously (12). cBSA was synthesized by coupling hexamethylenediamine to BSA with a carbodiimide-catalyzed reaction according to the published method (12). BSA and cBSA were labeled with ' ' ' In C13, using diethylenetriaminepentaacetic acid anhydride (Dojindo Labs, Kumamoto, Japan), according to the method of Hnatowich et al. (16). Preparation of MMCD. MMCDcal and MMCDan were synthesized as reported previously (4, 9). MMCD was radiolabeled by coupling 7-['4C]aminobutyric acid to dextran activated by cyanogen bromide, together with t-aminocaproic acid (['4C]MMCDcat) or to spacer-intro duced dextran together with MMC by a carbodiimide-catalyzed reac tion <[14C]MMCDan) (8). The radiolabel in MMCDs was stable and had behavior consistent with that of a dextran backbone. Animals and Tumors. Female SLC Wistar rats weighing 100 to 120 g were obtained from Shizuoka Agricultural Association for Lab oratory Animals, Shizuoka, Japan. The Walker 256 carcinoma was supplied by Shionogi & Co., Osaka, Japan, and was maintained by s.c. inoculation of rats every 2 weeks. Preparation of Tissue-isolated Tumors. According to the method of Cullino and Grantham (17, 18), rat ovarian tissue-isolated tumor was 4396 Downloaded from cancerres.aacrjournals.org on June 16, 2017. © 1992 American Association for Cancer Research. DISPOSITION OF MACROMOLECULES prepared as reported previously (14). In brief, three small blocks of Walker 256 carcinoma were inoculated into the adipose tissue around the ovary, enclosed in a Sealon film envelope (Fuji Film, Tokyo, Japan), then placed in the s.c. pouch of the abdomen. The tumor was grown in a "tissue-isolated" form and the film was changed after 1 week. About 2 weeks after tumor inoculation, tumor weighing 4-8 g was used for perfusion. Perfusion Experiment. The tissue-isolated tumor was perfused ac cording to the previous method (14) with slight modifications. Fig. 1 shows a diagram of the perfusion experiment. At first, all blood vessels supplying nontumorous tissues around the tumor (left renal artery and vein, left adrenal artery and vein, and aorta) were ligated. Immediately after ligation of the aorta, vinyl tubing (inside diameter, 0.5 mm; out side diameter, 0.9 mm; Durai Plastics & Engineering, Durai, Australia) was inserted into the aorta and the perfusate was infused at a rate of 0.8 ml/min. Vinyl tubing (inside diameter, 0.8 mm; outside diameter, 1.2 mm) was inserted into the tumor vein for outflow sampling. Finally, the tumor was transferred onto a plate in the experimental system. The tumor mass was perfused with Tyrode's solution (a mixture of 137 HIM NaCl, 2.68 mM KC1, 1.80 mivi CaCl2, 11.9 mivi NaHCO3, 0.362 HIMNaH2PO4, 0.492 ITIMMgCl2, and 5.55 HIMo-glucose) containing BSA at a concentration of 4.7% (w/v). The same medium was used for drug administration. The perfusate was gassed with 95% O2-5% CO2 and maintained at 37°C.Viability of the perfused tumor was confirmed by measurement of lactic acid production. The rate of production dur ing a 3-h perfusion experiment was within the range of 1.3-2.2 mmol/ h/100 g, which was comparable to that reported by Cullino and Grantham (17). In addition, the viable region subjected to s.c. inocula tion to normal rats after a 3-h perfusion showed almost the same growth rate as freshly prepared tumor, suggesting its viability. Indicator Dilution Experiment. Drug solution (0.1 ml) was intro duced from the arterial side of the tumor by using a six-position valve injector as a pulse function. The concentrations of the injection solu tions were 1 mg/ml for MMC and 100 Mg/mlfor [14C]MMCDcat(T-70). EB/BSA was used as a VRS and was applied prior to the drug injection to obtain basic physiological information for each tumor preparation. The drug solution was injected into the same tumor in the second run. The outflow was collected into previously tared tubes at appropriate time intervals (at first 5 s, subsequently 10 to 15s). The sample volume was calculated from the gain in weight of the tube by assuming the density of the perfusate to be 1.0. The concentration was determined by using a spectrophotometer at 620 nm for EB/BSA and 365 nm for MMC. To determine [14C]MMCDcal(T-70), 5 ml of scintillation me dium, Clear-Sol I (Nacalai Tesque, Kyoto, Japan) was added to the sample and 14C radioactivity was measured in a liquid scintillation system (LSC 900, Aloka, Tokyo, Japan). Pharmacokinetic Analysis of Indicator Dilution Experiment. Mo ment analysis was used to analyze dilution curves and the statistical reservoir in incubator IN ISOLATED TUMOR moment parameters are calculated as follows (19); -S: -J; AUC= | Cat (A) tCdt / AUC (B) o MTT where t is time and C is the concentration of a test substance normalized by injection dose with a dimension of percentage of dose/ml. AUC and MTT are the area under the concentration-time curve and the mean transit time, respectively. The disposition parameters representing the recovery ratio (F) and intrinsic clearance (CL¡m) are calculated from the moment parameters based on well-stirred conditions as follows (19); F=AUC/AUCV, CIinl = (2(1 - F)IF (O (D) where Q and AUCvrs are mean inflow rate and AUC of VRS. Constant Infusion Experiment. The drug-containing perfusate (10 Mg/ml) was infused at a rate of 0.8 ml/min into the tumor preparation for up to 180 min. At the end of infusion, drug-free perfusate was infused for 5 min to remove drugs remaining in the intravascular space. During these procedures, the venous outflow was collected into tared counting vials at appropriate time intervals. The sum of the outflow perfusate and exúdate from the tumor was almost the same as the inflow rate and no significant weight gain of the tumor during the perfusion was detected. After washing the intravascular space, the tissue was excised and carefully divided into viable and necrotic regions based upon macroscopic observation. The viable region is the whitish periph eral part of the tumor while the reddish and flabby necrotic region was usually found in the center. Histológica! observation confirmed that both samples essentially represented viable and necrotic tissues. These samples were minced into small pieces. To measure the level of 14Clabeled macromolecules, tissue sample (approximately 0.1 g) was placed into a counting vial and 0.7 ml of Soluene-350 (Packard, Down ers Grove, IL) was added. The mixture was heated overnight at 50°C, cooled to room temperature, and 0.18 ml of 2 N hydrogen chloride was added. The radioactivity in the tissue sample and outflow were deter mined in a liquid scintillation counter after adding 5 ml of scintillation fluid. The radioactivity of the "'In-BSA was directly determined by a Nal well-type scintillator (ARC-500, Aloka, Tokyo, Japan). Pharmacokinetic Analysis of Constant Infusion Experiment. Time courses of accumulation of [l4C]dextran(T-70) and [I4C]DEAED(T-70) in the tumor tissue were analyzed based upon a parallel flow model (Fig. 2). Here, a test compound, which is initially found in the vascular space at a fixed concentration (Co), permeates across the vascular wall, moves through the interstitial space, and finally oozes from the tumor tissue along with the convectional fluid flow. In this model, the macromolecule is directly distributed to the viable and necrotic regions by an independent convection flow with rates of Jv and Jn (ml/min/g). The osmotic reflection coefficient for the macromolecule is assumed to be zero throughout all processes. The macromolecule passes through the interstitial water space with a volume of V and interacts with tissue components. The degree of the interaction is expressed in terms of the distribution volume (K). Based upon the model, the following equations were derived to describe the concentration change in the viable (v) and necrotic (n) regions. dCv dt dCv' ~dT = Jv(Co - Cv') (E) (F) Fig. 1. Perfusion system of the tissue-isolated tumor preparation. where Cvand Cn are concentrations in the viable and necrotic regions 4397 Downloaded from cancerres.aacrjournals.org on June 16, 2017. © 1992 American Association for Cancer Research. DISPOSITION OF MACROMOLECULES Constant Infusion than 10% of the MMC was extracted by the tumor, whereas no significant difference was observed in the uptake amounts of [14C]MMCDca,(T-70) and VRS during a single passage after a Vv bolus arterial injection. Constant Infusion Experiment. Fig. 4 shows a typical out flow pattern of [14C]DEAED(T-70) during constant infusion Cv1 Viable Region Kv Co IN ISOLATED TUMOR Cv' for 180 min. The outflow concentration reached a plateau of almost 100% of the inflow concentration in three minutes, re mained at the same level during infusion, then declined imme diately after vascular washing. Essentially similar results were obtained for other macromolecules (data not shown). Fig. 5 illustrates the concentrations of all tested macromol ecules in the tumor tissue after a 180-inin infusion. Marked accumulation was observed in positively charged macromole cules such as [14C]MMCDcat(T-10), [I4C]MMCDca,(T-70), [14C]DEAED(T-70), and ['"InJcBSA. Furthermore, they Necrotic Region Kn Cn' Fig. 2. Pharmacokinetic models for analysis of the disposition of macromolecules in tissue-isolated tumor preparations after constant infusion. normalized by inflow concentration; Co is the inflow concentration (100%); J is the rate of convection flow (ml/min/g); C is the concen tration in the interstitial space (%/ml); and (V+ K) then corresponds to the apparent total distribution volume of the macromolecule per unit weight (ml/g). Integration of Equations E and F give. Jv = Co(Vv + Kv)\ 1 -exp Cn = Co(Vn + Kn)\ 1 -exp Vv + Kv - Jn Vn + Kn (G) showed higher concentrations in the viable than in necrotic regions. In contrast, the concentrations of neutral ([14C]dextran(T-lO), [14C]dextran(T-70), and [l4C]inulin) and negatively charged ([14C]MMCDan(T-70), [14C]CMD(T-70), and ['" In]BSA) compounds in the necrotic were relatively higher than those in the viable region. Pharmacokinetic Analysis of Disposition of Macromolecules. Tissue concentration-time profiles of neutral [14C]dextran(T-70) and cationic [14C]DEAED(T-70) in viable and necrotic regions were determined during constant infusion for up to 180 min (Fig. 6). Both compounds accumulated in the tumor (H) =- The concentration profiles were then fitted to Equations G and H by using the nonlinear regression program MULTI (20), to estimate the pharmacokinetic parameters. Vascular and interstitial water space volumes of the tissue-isolated tumor preparation were determined by using ¡l4C]dextran(T-70) and [14C]sucrose as intravascular and extracellular markers, respec tively. The tumor preparation was infused with perfusate contain ing [l4C]dextran for 5 min or [l4C]sucrose for 60 min, and the radio activity in each region of the tumor and in the outflow samples was measured without washing with drug-free perfusate. Vascular and interstitial water space volumes were calculated by using the following equations 0> (0 o -o C o co 1- —¿ o U 14C]Dextran in out flow (dpm/ml) o O O [I4C]Sucrose in tissue (dpm/g) Extracellular space (ml/g) = 100 •¿ I+— [l4C)Dextran in tissue (dpm/g) Vascular space imi gì = 1000 60 [l4C)Sucrose in outflow (dpm/ml) 120 180 240 300 Time (sec) Fig. 3. Typical dilution curves of [I4C]MMCDC,,(T-70) together with VRS (EB/BSA). •¿. EB/BSA; O. |14ClMMCDc.,(T-70). Each compound was injected separately into the same tumor. Interstitial space (ml/g) = Extracellular space —¿ vascular space. RESULTS Table I Moment and disposition parameters for MMC. ['<C¡MMCDM (T-70), unii I'RS (EB/BSA) from the indicator dilution experiment Indicator Dilution Experiment. Fig. 3 shows a typical dilu tion curve of [14C]MMCDcal(T-70) together with that of VRS in a separate run of the same tumor preparation. The outflow pattern of [14C]MMCDt.„,(T-70)was almost identical to that of VRS. On the other hand, the concentration profile of MMC in the outflow was lower in the initial phase and higher in the later phase than that of VRS (data not shown). Table 1 summarizes the moment and disposition parameters for MMC, [I4C]MMCDcal(T-70), and VRS. The analysis revealed that more Values arc calculated from the dilution curves obtained after a bolus arterial injection. Values are expressed as means of at least three experiments. doses/ml)7774.26850.37528.77538.4MTT(s)44.370.135.332.4F10 of DrugsEB/BSAMMCEB/BSA[I4C]MMCDC., (T-70)ADC(% 4398 Downloaded from cancerres.aacrjournals.org on June 16, 2017. © 1992 American Association for Cancer Research. DISPOSITION OF MACROMOLECULES IN ISOLATED TUMOR In Fig. 6, simulation curves generated by using the parame ters in Table 2 are also shown and relatively good agreement with experimental data was obtained. DISCUSSION o U 120 60 Time 180 (min) Fig. 4. Typical outflow pattern of (14C]DEAED(T-70) in constant infusion experiment. Perfusate containing [I4C]DEAED(T-70) at a concentration of 10 ¿ig/mlwere infused into tissue-isolated tumors for 180 min and the tumor was subsequently washed with drug-free perfusate for 5 min. The solid lines drawn through the points were fit by eye, postulating that the equilibrium was at a concentration of 100%. Generally, tumor tissues are characterized by enhanced vas cular permeability, high interstitial diffusion coefficients of macromolecules, and lack of a functional lymphatic system (21, 22). These characteristics seem to act as favorable factors for passive transport of blood-oriented large molecules to the tumor, and several investigators have reported the accumula tion of macromolecules in tumors after i.v. injection (12, 2325). Thus, tumor targeting using macromolecular drug carriers is rationalized by the physiological and anatomical character istics of tumor tissues. On the other hand, it has also been suggested that elevated interstitial pressure in tumor tissues restricts the extravasation and interstitial transport of macromolecules and leads to their heterogeneous distribution (2628). For monoclonal antibodies, furthermore, antigen-antibody interaction was shown to result in retarded penetration and nonuniform distribution in the tumor (29-32). However, de tailed information on the actual disposition of macromolecules in the tumor tissue remains to be elucidated. We performed perfusion experiments by using tissue-isolated tumor prepara tions to assess the effect of physicochemical properties of mac romolecules on their disposition in the tumor. 2 i oo e 1 50 rflrfl MMCDcal (T-10) MMCDcat MMCDan (T-70) (T-70) Dexlran IT-10) - H r-n Dexlran (T-70) DEAED CMD {T-70) (T-70) Fig. 5. Concentrations of radiolabeled macromolecules in viable (D) and necrotic i! il regions of tissue-isolated tumors after constant infusion for 180 min and subsequent washing for 5 min. Data are expressed as mean ±SD of the percentage of radioactivity in the tissue to that in the inflow perfusate, assuming the specific gravity of the tissue to be 1.0. *,statistically significant difference (P < 0.05, t test) between concentrations in viable and necrotic regions. tissue with time, and cationic [14C]DEAED(T-70) was accumu lated at higher levels. Prior to the analysis, the vascular volumes and the interstitial water space volumes of viable and necrotic regions were deter mined. The vascular volume in the viable region [0.0372 ± 0.0200 (SD) (N = 3)] was slightly larger than that in the necrotic region [0.0282 ±0.0178 (N = 3)] (no significant difference), whereas the extracellular space volume determined as equili brated sucrose space at 60 min in the necrotic region [0.281 ± 0.048 (N = 3)], was significantly larger (P < 0.05) than that in the viable region [ 0.194 ±0.019 (N = 3)]. Interstitial water space volumes calculated as the difference between these vol umes are shown in Table2 and are used for the pharmacokinetic analysis. Table 2 summarizes the parameters estimated by data fitting the tumor concentration profiles based on the pharmacokinetic model. The total distribution volumes of [14C]dextran(T-70) for viable and necrotic regions were 71.7 and 57.7% of the inter stitial water space volumes, respectively. On the other hand, those of [I4C]DEAED(T-70) were 9.8- and 7.0-fold larger than the interstitial water space volumes, respectively. The convec tion flow rates were estimated to be 0.011 and 0.005 ml/min/g in the viable and necrotic regions, respectively. 120 240 Time 360 (min) Fig. 6. Concentration-time profiles and simulation curves of neutral [I4C]dextran(T-70) and cationic (I4C]DEAED(T-70) in the tissue-isolated tumor prep aration after constant infusion. •¿, [14C]dextran(T-70) (viable region); O, |14C]dextran(T-70) (necrotic region); •¿. [I4C]DEAED(T-70) (viable region); D, [14C]DEAED(T-70) (necrotic region). Each value represents the mean ±SD of the percentage of radioactivity in the tissue compared with that in the inflow perfusate after infusion for each time period and subsequent washing. The specific gravity of the tissue was assumed to be 1.0. '.statistically significant difference (P < 0.05, f test) between concentrations in viable and necrotic regions. The simulation curves were generated by using the pharmacokinetic parameters from Table 2. Table 2 Interstitial space volumes and pharmacokinetic parameters for ["CJdextran (T-70) and ["CJDEAED (T-70) in the tissue-isolated tumor Numbers in parentheses are percentages to the respective interstitial space volume. The abbreviations are: J, convection flow rate; y + K, total distribution volume. K(ml/g) J (ml/min/g) y+ tf(ml/g) [l4C]dextran (T-70) ¡14C]DEAED(T-70)Viable region0.157 region0.253 0.01120.113(71.7) 0.00500.146(57.7) 1.530(975)Necrotic 1.73 (701) 4399 Downloaded from cancerres.aacrjournals.org on June 16, 2017. © 1992 American Association for Cancer Research. DISPOSITION OF MACROMOLECULES We at first performed indicator dilution experiments, with which we previously evaluated the disposition of low molecular weight antitumor drugs (14), whose extraction by the tumor occurred depending on their lipophilicity as shown for MMC (Table 1). However, the macromolecules tested in this study had similar dilution curves to that of VRS (Fig. 2), indicating similar behavior to VRS at the extraction step. In addition, only a slight decrease in the perfusate concentration of cationic mac romolecules was observed during single passage under the steady-state condition in the constant infusion (Fig. 4). These results are contrasted to our previous findings in the liver, where cationic macromolecules were extensively taken up through discontinuous endothelium, which allows free contact of macromolecules with the surface of the parenchymal cells (33). The present facts indicated that architecture of vascular wall is essentially tight in the tumor, unlike the liver, although tumors should have permeable vasculature. The binding of mac romolecules to capillary endothelium was also suggested to be negligible. In the tumor tissue, convection is considered to be the dom inant mechanism of macromolecular transport (34), although it is a relatively slow process. Therefore, we measured the accu mulation of macromolecules in the constant infusion system to elucidate the effects of their physicochemical properties (Figs. 5 and 6). Positively charged macromolecules were markedly ac cumulated in the tumor, in particular in the viable region, which was a well-perfused part. In contrast, those negatively charged or neutral macromolecules were accumulated at lower levels, and were characterized by being at a relatively higher level in the necrotic region. The molecular weight had little effect in the tested range (A/r 5,000-70,000). From the data in Fig. 5, the apparent tissue uptake clearance can be calculated by dividing the tissue concentration by the AUC of the compound in the perfusate (11). The values for cationic [14C]DEAED(T-70), which was markedly accumulated in the tumor, were 6.2 and 3.8 ^l/min/g for the viable and necrotic regions, respectively. Then, recovery ratio (F) of a macromolecule in the outflowed perfusate during the constant in fusion is calculated as follows Inflow rate - tissue uptake clearance F = Inflow rate Assuming the tumor weight to be 6 g and weight ratio of viable and necrotic regions to be 5:1, F is calculated to be 0.957 for [14C]DEAED(T-70). At first glance, this value appears to be inconsistent with the results described in Fig. 4, where the outflow concentration was almost equal to inflow concentra tion. Furthermore, indicator dilution experiments showed no significant difference in uptake of [14C]MMCDca,(T-70) and VRS. These discrepancies can be explained by the hypothesis that the macromolecule is conveyed into the interstitial space by convective flow. The concentration in the perfusate would not change before and after passage through the tumor and the macromolecule would have the same dilution curves as that of VRS. The tissue uptake clearance is an apparent index offering only phenomenalistic information equivalent to that in Fig. 5 and no information about the accumulation mechanism. There fore, we analyzed the accumulation process of macromolecules with a pharmacokinetic model (Fig. 2), assuming convective transport and tissue binding. IN ISOLATED TUMOR We determined the vascular and interstitial water volumes of viable and necrotic regions for comparison with the apparent distribution volumes of macromolecules. The reported values of the vascular space in Walker 256 carcinoma varied to some extent, depending on the marker substance (35). Song and Lev itt (23) reported that the average vascular volume of s.c. im planted Walker 256 carcinoma (0.01-4 g tumor) was 0.8%, using 51Cr-labeled erythrocytes. Cullino and Grantham (36) determined the vascular volume of tissue-isolated Walker 256 carcinoma (3.5-13 g tumor) with dextran 500 (Mr 37,500) tobe 10.8%. In a previous study, we reported the vascular volume of tissue-isolated Walker 256 carcinoma (1-20 g tumor; mean, 8.71 g) to be 7.0% using EB/BSA (17). The vascular volumes determined in the present study with dextran(T-70) (3.7 and 2.8% for viable and necrotic regions, respectively) were within these values. However, leakage of dextran, especially in the necrotic region, or contamination between these regions, might be included in these values. On the other hand, the interstitial water spaces determined in the present study (15.7 and 25.3% for viable and necrotic re gions, respectively) were smaller than that reported by Cullino et al. (37) (38.7%) obtained by direct measurement of 24Na in tissue fluid of Walker 256 carcinoma (4.7-10.4 g). Although some differences were observed between these studies, we used our values since those for viable and necrotic regions were sep arately available. Analysis of the accumulation pattern of cationic [I4C]DEAED(T-70) revealed that the apparent distribution volumes in the viable and necrotic regions were 7 to 10 times higher than those of the interstitial water volumes (Table 2), indicating strong binding to the tissue. On the other hand, the apparent distribution volumes for neutral [14C]dextran(T-70) were smaller than the interstitial volumes. Our previous studies in vitro demonstrated that MMCDcal and other cationic macromolecules bound with leukemia cells (8) and solid tumor cell layers grown on microporous mem branes (38) due to electrostatic interactions. The same mecha nism can account for the interaction of positively charged mac romolecules with the tumor cell surface and components in the interstitium. In contrast, negatively charged or neutral macromolecules would only be distributed in the interstitial fluid, without any tissue interaction. The sum of the convective flow (0.061 ml/min) calculated in the viable and necrotic regions with a weight ratio of 5:1 ap proximately corresponds to 7.7% of perfusion flow rate for 6 g of tumor. In another study, we determined the rate of fluid loss in isolated tumors with a mean weight of 6.36 g to be 16.6% from the outflow recovery. Butler et al. (39) reported that extravascular fluid loss was 10.2% of the perfused plasma volume in Walker 256 carcinoma (mean, 3.8 g tumors). These values essentially correspond to our estimated convective flows, sug gesting the reliability of considering convective flow as a driving force of macromolecular movement. The heterogeneous distribution in the tumor shown for cationic macromolecules in this study may be an obstacle to tumor targeting with macromolecular carrier systems including mon oclonal antibodies (26). A possible approach to overcome this problem may be the use of the prodrug concept; i.e., regenera tion of the parent drug in the interstitial space. The regenerated free drug can readily distribute over the whole tumor mass by diffusion, even if the movement of the prodrug (drug-macromolecule conjugate) itself is prevented by strong binding or a 4400 Downloaded from cancerres.aacrjournals.org on June 16, 2017. © 1992 American Association for Cancer Research. DISPOSITION OF MACROMOLECULES high interstitial pressure. MMCD was shown to liberate free MMC by simple chemical hydrolysis (5), and it is implied that local constant infusion of MMCDcal might be effective for intensive exposure of the tumor tissue to MMC irrespective of its limited movement. However, further studies are required to confirm whether regenerated MMC actually reaches into the tumor cell itself. Thus, the present study demonstrates the basic disposition characteristics of macromolecules in a tissue-isolated tumor preparation and the importance of their electric charge. These findings will be useful for the development of macromolecular prodrugs aiming at targeted cancer chemotherapy. REFERENCES 1. Sezaki, H., Takakura, Y., and Hashida, M. Soluble macromolecular carriers for the delivery of antitumor drugs. Adv. Drug Delivery Rev., 3: 247-266, 1989. 2. Vogel, C-W. Current approaches of immunoconjugating. In: C-W. Vogel (ed.), Immunoconjugates: Antibody Conjugates in Radioimaging and Ther apy of Cancer, pp. 3-7. New York: Oxford University Press, 1988. 3. Sezaki, H., and Hashida, M. Macromolecule-drug conjugates in targeted cancer chemotherapy. CRC Crit. Rev. Ther. Drug Carrier Syst., /: 1-38, 1984. 4. Kojima, T., Hashida. M., Muranishi, S., and Sezaki, H. 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Disposition Characteristics of Macromolecules in the Perfused Tissue-isolated Tumor Preparation Hirofumi Imoto, Yumi Sakamura, Kazuhiro Ohkouchi, et al. Cancer Res 1992;52:4396-4401. Updated version E-mail alerts Reprints and Subscriptions Permissions Access the most recent version of this article at: http://cancerres.aacrjournals.org/content/52/16/4396 Sign up to receive free email-alerts related to this article or journal. To order reprints of this article or to subscribe to the journal, contact the AACR Publications Department at [email protected]. To request permission to re-use all or part of this article, contact the AACR Publications Department at [email protected]. Downloaded from cancerres.aacrjournals.org on June 16, 2017. © 1992 American Association for Cancer Research.