WO1981003072A1

WO1981003072A1 - Method and apparatus for automatic dissolution testing of products

Info

Publication number: WO1981003072A1
Application number: PCT/US1981/000423
Authority: WO
Inventors: V Smolen
Original assignee: V Smolen
Priority date: 1980-04-17
Filing date: 1981-03-31
Publication date: 1981-10-29
Also published as: JPS57500484A; CA1145158A; EP0049293A1; EP0049293A4; US4335438A; DK539481A

Abstract

A method and apparatus for optimally performing dissolution testing of pharmaceutical dosage forms, agricultural products, and components of industrial products wherein the method uses dissolution profiles from a known drug dosage form, or product, as reference data for a predictive process; and the apparatus is organized to carry out the method via both closed loop and open loop operating modes under the control of a central processor (56). An illustrative embodiment teaches the serial usage of the two operating modes in a single flow-through dissolution cell configuration (12) to optimally predict the time course of in vivo bioavailability from in vitro dissolution measurements, while an alternate embodiment teaches the use of a plurality of dissolution cells (12) and the simultaneous use of the closed and open loop operating modes to implement an Internal Standard capability. Additionally, an optimally adaptive capability is provided in the dissolution testing process via a random input modeling mode of operation.

Description

METHOD AND APPARATUS FOR AUTOMATIC DISSOLUTION TESTING OF^'PRODUCTS

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention relates generally to the field of automatic dissolution testing of products whose solubility and dissolution rate properties affect product performance, and more specifically to the optimal prediction of product dissolution characteristics using known product data as a reference for a feedback controlled apparatus. The methods disclosed and the electronically controlled apparatus described are presented in connection with in vitro dissolution testing of pharmaceutical drug dosage forms to predict in vivo bioavailability. However, both the methods and apparatus taught are equally applicable to dissolution testing of agricultural products formulated as controlled release herbicides, insecticides, fertilizers, and the like; and further to the dissolution testing of components of industrial products including solid materials whose solubility properties depend on a wide variety of factors.

2. Description of the Prior Art

Dissolution testing of components of industrial products whose solubility and dissolution rate properties

^~- ^r7.^χ " .τ. -^~ ' " ^■ CΓ T -^*H ^■ . affect product performance can be used as a screening and quality control tool. The solubility properties of solid materials can depend on polymorphic crystalline form, crystal habit, crystal shape, particle size and particle size distribution, and state of solvation. A simple and rapidly performed dissolution test can substitute for the determination of these physical properties by more time consuming and expensive methods such as x-ray crystallography, differential thermal analysis, microscopy, etc. The materials are instead determined as to whether they conform to a dissolution rate standard under specified conditions and in relation to a known reference sample of the same material characterized by th above physical properties and possessing the derived dissolution rate and solubility performance.

The broad technique of determining dissolution rate properties is especially of interest in the testing of drug products where the therapeutic performance of drugs is closely related to the drug dissolution properties. Seemingly minor changes in drug product formulation, as well as the inadvertent variation in materials and manufacture that can occur between batches of the same product formulation, can influence the therapeutic performance of drugs. In vivo bioavailabilit testing of drug products in humans provides the most reliable means of ensuring bioequivalence. However, it i impractical to perform the extensive and expensive human testing that would be routinely required. Large numbers of human subjects would be placed at risk if such studies were conducted. Bioavailability testing in which humans are used as test subjects can be minimized by the development and implementation of in vitro dissolution standards that reflect in vivo drug-product performance . In vitro bioequivalence requirements have been establishe for some drugs such as digoxin. From among the various chemical and physical tests that can be performed on drug solids in vitro for correlating or predicting a drug product's in vivo bioavailability behavior, dissolution testing is the most sensitive and reliable. The correlative relationships most commonly reported between in vitro dissolution and in vivo bioavailability are of the single-point type: the percentage of the drug dissolved in a given time (or the time it takes to dissolve a given percentage of the drug in vitro) and some univariate characteristic of the drug product's in vivo response versus time profile (such as the peak blood level, the time required to reach the peak or 50% of the peak, or the area under the blood-level curves) are correlated. The selection of in vitro dissolution and in vivo bioavailability perameters for such single-point correlations is frequently arbitrary, and the results can be misleading. Obviously, it would be preferable to predict the entire average blood level, urinary recovery rate, pharmacological-response-time, or drug absorption rate vs. time profile that would be elicited by adrug product in a panel of human subjects rather than merely to correlate univariate characteristics of the dissolution profile with an in vivo bioavailability parameter. In all cases, however, the fidelity of the in vitro dissolution results in correlating and in predicting in vivo drug-product bioavailability depends upon the dissolution-test process variables, such as the dissolution-medium composition, the solubility volume of the medium (sink conditions that determine the extent to which the medium becomes saturated with the drug), and the agitation rates (stirring or flow rates). An improper choice of these process variables (e.g., an excessively high rate of agitation) can mask significant bioavailability differences among drug products. On the other hand, the dissolution test can be overly sensitive in detecting differences that are negligible in vivo. In the former case, using such improper dissolution-test parameters would result in the marketing of therapeutically ineffective drug products. In the latter case, the result would be the discarding of drug products that are entirely satisfactory in terms of in vivo performance. Serious economic losses could result from the use of an overly sensitive in vitro dissolution test for lot-to-lot reproducibility testing of drug products . Therefore, whether the dissolution test is being used as quality control tool, as an in vivo bioequivalency requirement for multisource generic drug products, or as substitute for human bioavailability testing during the development of new drug-product formulations, it is imperative that the dissolution test provide predictive results that are biologically relevant.

Developing drug-product dissolution tests that predict the time course of drug-product bioavailability can be fraught with pitfalls, some of which may be avoide through knowledge and consideration of the physiochemical properties of the components of the drug product and the biological processes and conditions operative in the release of the drug from the gastrointestinal tract and its subsequent absorption. However, it is not only futile, but also unnecessary to attempt to reproduce the complex of biological factors- operating in vivo in the effort to develop a satisfactory in vitro bioavailability test, although such attempts have been made. The devices that resulted from these efforts are of value now only as museum pieces. It would, however, be imprudent to ignore such knowledge when it can be used advantageously to circumvent a problem in the design of a dissolu-ion test.

There are two possible general aproaches to developing in vivo relevant drug product dissolution tests. Both approaches seek to predict the entire time

- ^■ course of average blood levels that would be observed for a drug product in a panel of human test subjects. In this way, the dissolution test serves as a substitute for human testing. The first approach is a computational method that maximizes the amount of information that can be obtained from conventional methods of in vitro dissolution testing. Used most frequently are the USP rotating-basket apparatus, the FDA paddle method, the stationary-basket/ rotating filter apparatus, Sartorius solubility and absorption simulators (Sartorius, Incorporated, Hayward, California), and column-type flow-through assemblies. The last of these devices offers advantages with regard to the defintion, flexibility of control, standardization, and reproducibility of process variables. This apparatus has been used by the inventor of the present invention to demonstrate the second approach to predicting in vivo blood-level curves that emerge from the apparatus in the form of dissolution rate versus time profiles. Since the computational approach with conventional apparatus depends upon the relatively arbitrary selection of process variables, its usefulness is limited. However, using feedback control to continuously vary the process variables, as described below, obviates this problem. For a more complete treatment of the mathematical (and theoretical) aspects of the dissolution, the interested reader is directed to three papers co-authored by the inventor. These are.: V.F. Smolen et al, "Optimally Predictive In Vitro Drug Dissolution Testing for In Vivo Bioavailability," J. Pharmaceutical Sci., Vol. 65, No. 12, pp. 1718-1724, December 1976; V. F. Smolen et al, "Predicting the Time Course of In Vivo Bioabailability From In Vitro Dissolution Tests: Control Systems Enginering

* " Approaches," Pharmaceutical Technology, pp. 89-102, June 1979; and V.F. Smolen et al, "Predictive Conversion of In-Vivo Drug Dissolution Data into In Vivo Drug Response Versus Time Profiles Exemplified for Warfarin," J. Pharmaceutical Sci., Vol. 66, No. 3, pp. 297-304, March 1977.

The present invention is directed to an improved method and apparatus for carrying out the dissolution approach to optimally predicting in vivo drug bioavailability from pharmaceutical dosage forms, and other applications of dissolution testing.

SUMMARY OF THE INVENTION It is therefore a primary object of the presen invention to provide improved methods and apparatus for performing dissolution teting of pharmaceutical dosage forms, agricultural products, anc components of industria products whose solubility and dissolution rate properties affect product performance.

Another object of the present invention is to provide improved methods and apparatus for predicting in vivo bioavailability of drug dosage forms from in vitro dissolution testing.

Another object of the present invention is to provide methods and apparatus for dissolution testing of industrial products, including drug dosage forms, agricultural products, and the like, wherein a closed loop control process is first used to initialize the control loop process variables while operating on known reference data, and an open loop control process is then used to perform the predictive process using the process variables previously derived.

Another object of the present invention is to provide methods and apparatus for dissolution testing of plurality of industrial products, including drug dosage

"

forms, agricultural products, and the like, simultaneously, using an operating mode wherein closed loop and open loop control processes are accomplished concurrently using a known product formulation and its corresponding dissolution profile as reference data, to implement an Internal Standard operating mode.

A still further object of the present invention is to provide an improved dissolution testing apparatus including a dissolution cell having proportional agitation means and to further provide an optimally adaptive capablity into the dissolution testing process via a random input modeling mode of operation. *

BRIEF DESCRIPTION OF THE DRAWINGS Additional object and advantages of the invention will become apparaent to those skilled in the art as the dexcription procees with reference to the accompanying drawings wherein: .

FIGURE 1 is an overall block diagram of the automatic dissolution testing system according to the present invention;

FIGURE 2 is a simplified block diagram of the closed loop programmed control of the automatic dissolution testing system;

FIGURE 3 is a simplified block diagram of the open loop control system implemented in the automatic dissolution testing system;

FIGURE 4 is an overall block diagram of the dissolution testing system expanded to show operation in the Internal Standard mode; and FIGURE 5 is an overall block diagram of the closed loop control system for use with an improved bioavailability predictive embodiment of the present invention.

!! \ DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

Referring now to Figure 1, there is shown an overall block diagram of the automatic flow-through dissolution testing system according to the present invention. For simplicity of exposition the various elements are not shown to scale, and the embodiment shown is a basic one. The descriptions throughout this specification are expressed in terms of the testing of a pharmaceutical drug dosage form, and the language is accordingly specific to this usage. Of course, the embodiments disclosed are illustrative and could readilty be adapted for use with agricultural products, or with controlled release components of industrial products generally. The overall system 10 is shown as comprised o a basic dissolution cell 12 in which is positioned a specimen of the drug product 14 undergoing evaluation. The cell 12 has a filter membrane 12A and filter screen 12B, and is provided with a flow of various dissolution liquid via a cell input line 16 under the influence of a primary pump 18. Output from the dissolution cell 12 is carried by a cell output line 20 and is routed first via the upper portion of a recirculation line 22, and thereafter via a system output line 24. Within the recirculation line 22 is a recirculation pump 26 which propels the liquid therein into the lower portion of the recirculation line 22, and thereafter into a feeder line 28, which serves as an input to the primary pump 18. The two arrows 30A and 30B show the direction of flow in the recirculation line 22 under the influence of the recirculating pump 26.

A first reservoir 32 is used to contain a supply of a first dissolution medium 34, which is fed via a line 36 to the dissolution cell 12. The first dissolution medium 34, hereinafter alternately called the acid media, is fed to the feeder line 28 under the

c- . * r- <r . ' influence of a pump 38. The flow direction of the acid media 34 is shown by the flow arrows 40A and 40B. A second reservoir 42 is used to contain a supply of a second dissolution medium 44, hereinafter alternately called the alkaline medium 44. The alkaline medium 44 is fed via a line 46 and a check valve 48 to the feeder line 28, and subsequently through the primary pump 28 to the dissolution cell 12. The flow direction of the alkaline media 44 is shown by the flow arrows 50A and 5OB. As will be discussed in detail below, the flow path 40B of the acid media 34 is due to the presence of the check valve 48, and the flow path 50B on the alkaline medium 44 is due to the dynamics of the action of the two pumps 38 and 18. The system output line 24 serves to conduct the flow of the processed media containing the desired concentration of the dissolved drug product out of the system, and further supports two key system measurements . A flow measurement device 52, serially positioned in the output line 24, provides a quantitative measurement of a liquid flow rate via a group of lines 54 to a central processor 56. (Alternatively, this flow rate may be obtained electronically as the difference in control signals to the primary pump 18 and the recycle pump 26.) A spectrophotometer 58, also serially positioned in the output line 24, provides a periodic (or continuous) measurement of the drug concentration in the output flow, and routes this measurement via a group of lines 60 to the central processor 56. Pumps 18, 26 and 38 are of the positive displacement peristaltic type and are capable of producing precisely controlled flow rates in the range of 0.2 to 140 ml per minute when properly controlled. The central processor 56 provides this control via signals on three gropus of lines 62, 64 and 66 which modulate the excitation to the pumps as follows. Control signals on the line 62 are applied to a pump speed modulator 68, which in turn controls the excitation of the pump 26 via the lines 70; control signals on the lines 64 are applied to a pump speed modulator 72, which in turn controls the excitation of the pump 18 via the lines 74; the control signals on the line 68 are applied to a pump speed modulator 76, which in turn controls the excitation to the pump 38 via the lines 78. In addition to the above three control signals, the central processor 56 further provides control signals to an agitation means comprised of a stirring paddle 80 located within the dissolution cell 12 and positioned below the filter screen 12B. These control signals are provided on a group of lines 82 to an inteface device 84. An output from the interface device 84 is applied via lines 86 to an agitation motor 88, which in turn activates the stirring paddle 80 via the mechanical linkage shown as dashed lines 90. A group of control and data lines 92 interconnect the central processor 56 with a number of supporting units shown as a peripherals group 94. Included within this group 94 would be a data recorder 94A (analog and/or digital), an output printer 94B, and input keyboard 94C, and other well known and conventional devices. An overall measurement block 96 identified those elements considered to be measurement apparatus, as compared to the remaining elements — 56 and 94 — which may be considered to be the signal processing and control portions of the system.

In use, the system of Figure 1 carries out the dissolution testing under the control of the central processor 56 as follows. By way of a brief overview, the system shown is operable in two modes, the first being a simulative (or closed loop mode) and the second being a predictive (or open loop mode) . First, a known drug dosage from is used to "calibrate" the apparatus by operating it in the closed loop mode using known in vivo data (from the recorder 94A) on the particular drug dosage

OMPI form to optimize a number of key parameters (hereinafter alternatley referred to as the process variables) within the central processor 56. An iterative optimizing process may be used to systemmatically modify the process variables until the difference between the measured (in vitro) data and the known (in vivo) data are minimized, and independent of time. Secondly, predictive tests of unknown drug dosage forms are performed using open loop control of the apparatus employing the previously determined values of the process variables. To accomplish these steps, control (proportional, differential and integral) is exercised over one or more of the process variables determined by: (1) the composition; (2) the recycle flow of the dissolution medium; (3) the tital flow rate of the dissolution medium; and (4) the rate of agitation within the dissolution cell.

During the course of the closed loop phase of the operation, a change in the medium pH can be used to simulate the in vivo change from the stomach to the duodenum, and the recycling of the medium to dissolution cell 12 allows variable sink conditions to be achieved to simulate the existing in vivo conditions due to differing barrier properties of drug absorbing biological membranes . Resistance to biological absorption is simulated by mixing the fresh media with the solution leaving the cell. The recycling of solution through the dissolution cell in this manner decreases the driving force for dissolution. Upon establishing desired constant flow rate at the outlet of the dissolution cell as determined by the flow measuring device 52, the time varying recycle flow rate, and a changing flow from the gastric and intestinal juice reservoirs are initiated. The spectrophotorαeter 58 provides a measurement of the concentration of the drug in the liquid leaving the cell. An alternate configuration may include placing the spectrophotometer on the recycle

c? "-_ flow line. This measured concentration value is compared within thecentral processor 56 with the known in vivo bioabailability rate, blood leve, urinary recovery rate, or pharmacological response versus time profiles being simulated. Any error signal produced is converted with the centrol processor 56 so as to optimize the process variables driving the error signal to a minimum value ._

A detailed description of the operation of thi system of Figure 1 is facilitated with additional reference to the block diagrams of Figures 2 and 3.

Figure 2 shows a block diagram for the closed loop contro of the dissolution testing system in the simulative mode; while Figure 3 shows a block diagram for open loop contro of the dissolution testing system in the predictive mode. Both the time variable form: R(t), and the transform variable form: R(s) of the system parameters will be use herein (interchangeably as required) as is well known in the control system art. The following process variables are applicable: Q(t) = volumetric flow rate (milliliters per minute) Q^. = Q/A = velocity through the cell

(centimeters per minute) AC = cross-sectional area of the cell (square centimeters)

R(t) = volumetric flow of recycle (milliliter per minute) ; i.e., it can be a constan or time-varying quantity M(t) — stirring rate within one dissolution chamber

F-_j_(t) = fraction of the solvent which is drawn from the reservoir containing, for example, simulated gastric juice, water, or an organic solvent (34 of FIG. 1)

SUBSTETϋTΞ F2( ) = fraction of one slvent which is drawn from the reservoir containing, for example, simulated intestinal juice, 1.0 normal sodium hydroxide, or an organic solvent (44 of FIG. 1).

The dissolution process extant within the system of FIG. 1 may commonly be described by a smple diffusion layer model:

where

dw = dissolution rate (milligrams per minute)

D = diffusion coefficient for the solvent and solute under consideration (square centimeters per minute) - .affected by dissolution media composition S = surface area for dissolution (squate centimeters) - an intrinsic property of the material (dosage form) being tested

C_s = concentration of solute required to satureate the solvent (milligrams per milliliter) - affected by dissolution media composition

C = actual solute concentration in solution (milligrams per milliliter) - affected by recycle flow and total volume flow

T = effective thickness of the film or diffusion layer (centimeters) - affected by agitation rate and total volume flow rate.

ezf. spq r^' The relationship between variables in the diffusion layer equation and the process variables are seen as given for fixed value of A^:

T — a function of Q and agitation rate C = a function of the volume of the dissolution chamber, V, and the volumetric flow rate, Q, i.e., the residence time, V/Q, and the flow of recycle, R or R(t). To avoid changing the volume of the dissolution chamber by changing its length to change C, this could also be effected by changin the recycle flow C_s = a function of the properties of the solvent. For example, using simulated gastric and intestinal juices mentione previously, the process variables to b manipulated here are F-_j_ and F2• The variables D and C_s are obviously affected by the solvents used and the relative proportions of each composing the dissolution medium at any time. When the solvent mixture is specified, D and C_s are also reflective of the properties of the solid being dissolved. S = in addition to being a function of Q, function of the initial amount of drug m_Q/ and the physical properties of the solid. Once these variables are fixed, i.e., once a drug and a dosage form are decided upon, the time course of S as the experiment proceeds is reflective of the properties of the drug products.

Referring first to FIG. 2, closed loop operation (simulative) in its basic form is shown as having an input signal A(S) — cumulative in vivo availability — applied to an input node where it is differenced with a feed back signal C(S) — concentration of the stream leaving the dissolution cell — to produce an error signal E(S). The error signal E(S) is applied to the input of a proportional-integral-derivative (PID) controller having the gain characteristic (alternately transfer function) G_C(S). The output from the PID controller is a signal M(S) suitable to operate the respective actuators in the system. The four actuators of FIG. 1 include three proportional controlled pumps and one proportional controlled motor. These actuators are represented simply as having a particular transfer function G (s), whose outputs are characterized by the four process variables R(S), M(S), Q(S), and F₁(s) — all as described below. The process variables are applied to the dissolution equipment having a transfer function G_DE(S) whose outpu is the desired parameter C(S) or Q_S(S) C(S) — as described below. Briefly, FIG. 2 depicts in conventional analog-like terms the simulative function of the dissolution testing system. The analog-like descriptive terminology is used for simplicity and, of course, digital embodiments may be used to implement the control loop contemplated. During this closed loop (simulative, or calibration run) operation, three key parameters within the PID controller are optimized as described below such that subsequent open loop operation as shownin FIG. 3 constitutes an optimally predictive operating mode. As shown in FIG. 3, the open loop control system block provides optimized values of M(t), R(t), F-_]_(t) and Q(t) to the actuators (servo driven pumps, and/or motors) which in turn impact on the dissolution cell block to produce the desired output C(t) or Q_s(t) C(t) as above described. The objective of the system of FIG. 1 is to obtain results that uniformly reflect the in vivo drug availability with optimal fidelity over time and varying drug release behavior of the dosage forms. For any given set of process variables, i.e., Q_A# F_j_, (^F2 ⁼

1-F^), the closed loop operation of the in vitro testing apparatus will produce a function

(t) for each ith dosage form so that the expression ^"

CA_i(t)-CQ(t)-R_i(t)]C(t)] or [A_i(t)-C(t)] closely approximates zero. Functions R^(t), M^(t), Q_j_(t) and F-_j_._j_(t) will be obtained for each dosage form of the drug tested that was chosen to possess different drug release dynamics. These functions can be read out by the central processor 56 onto magnetic tape, stored on magnetic disc, or in the central memory of the microprocessor during the closed loop operation of the apparatus.

At this stage, the apparatus merely simulates the A(t) functions determined from in vivo experimentation. Analog R_j_(t) function signals recorded on magnetic tape for each dosage form can be conveniently processed on the central processor 56 and their values ca be averaged, over dosage forms, at each time to obtain anaverage, R(t) function representing the mean behavior o all dosage forms included in the closed loop operations . A second set of open loop runs must then be performed for each dosage form with the R(t), M(t), F₁(t), and Q(t) functions programmed to control the process variables . The number of closed loop runs performed on different dosage forms of the same drug and the resulting number of C^(t) functions and the corresponding number of R_j_(t), M_j_(t), Q_j_(t) and -,_-•_(t) process variables included in the R(t) , M(t), Q(t) and F-^t) functions will depend on the properties of any specific drug and the drug release characteristics of the dosage forms being tested.

+-<* i* ^2 * _ _ _** _ __ --'' If the dynamics of the in vivo and in vitro system approximate linear behavior, then only one reference dosage form is required. When appropriate, an objective function F_Q can be formed from the M(t), F-^ ), Q(t) , R(t), C_j_(t) and A(t) functions. A minimal value of the objective function is achieved by systematically selecting different solvents, geometries of the agitator, or if one or more process variables are kept constant, different fixed values of the process variables not allowed to continuously vary with time. A minimum value of the objective function corresponds to optimal open loop operation of the apparatus under such conditions. As mentioned, various means can be implemented to control the recycle flow dynamics. The system fo Figure 1 should be operated in the simplest manner that provides acceptable in vitro results with regard to in vivo drug availability behavior. To determine the magnitude of sensitivity of the fidelity of the test to different operating conditions, the test can be initially performed in successive phases of increasing complexity and equipment requirements.

Phase I can be performed without any automatic control, using fixed, time invarient, values of the process variables, M. F-_j_, Q, and R. An optimal composition and pH of the dissolution medium may be found and thereafter maintained constant.

Phase II can be performed similarly to Phase I but with the inclusion of automatic control of M(t) as a process variable. Phase III can employ automatic computer control of a time-varying dissolution media composition F-^(t) in addition to M(t).

Phase IV can add R(t) as an automatically controlled process variable. Phase V can utilize M(t) , F_χ(t), R(t) and Q(t) as automatically controlled process variables.

The order in which automatic control of the process variables is introduced depends upon the properties of the drug, e.g., such as its solubility and intrinsic dissolution rate in different solvents.

These submodes of operation can be repeated fo different dosage forms of the same drug to obtain the optimal conditions over all reference dosage forms. The simplest mode of operation possessing an acceptable fidelity would then be chosen for future studies with the drug.

For a somewhat more comprehensive description of the mathematical factors involved in the above, the interested reader is referred to the aforementioned 1976 article authored by the inventor. A more theoretical treatment of the relationship summarized above is also contained in an additional paper - V.F. Smolen, "Theoretical and Computations Basis for Drug Bioavailability Determinations Using Pharmacological Data II Drug Input Response Relationships," J. Pharmacokinetics and Biopharmaceutics, Vol. 4, No. 4, pp. 355-375, 1976.

Referring to Figure 4, there is shown an overall block diagram of an alternate embodiment of the present invention directed to producing the desired predictive dissolution profile action in an Internal Standard operating mode. The embodiment shown in particularly advantageous in the testing of a number of drug dosage forms simultaneously, by comparison to a reference drug dosage form - and may be used for simultaneously testing large batches of a single drug dosage form, or of simultaneously evaluating a number of different drug dosage forms. The apparatus is basically parallel arrangement of a plurality of single flow-throug

y :- dissolution systems as shown in Figure 1, using a single central processor/peripheral for control. The Internal Standard system 100 is shown as comprised of the elements of the embodiment of Figure 1, in the form of a central processor 56 interconnected with a peripherals groups 94 via a group of lines 92. A trunk of input/output lines 102 from the central processor 56 are routed to a reference dissolution testing subsystem 10R, via a group of input/output lines 102R; and to a first unknown dissolution testing subsystem 10A via a group of output lines 102A; and further to an "Nth" unknown dissolution testing subsystem ION via a group of output lines 102N. The number of independent dissolution subsystems may be fairly large — a dozen, or more — being limited by purely perfunctory considerations such as cost and convenience in usage. With continued reference to Figure 4 and occasional reference to Figure 1, the subsystems 10R, 10A, ION (of Figure 4) may be identical to the measurement block 96 (of Figure 1). The subsystem 10R, in combination with the central processor 56, the peripherals group 94 and the interconnecting lines 92, 102 and 102R constitute a dissolution testing system identical to that of Figure 1, operating in the closed loop mode of operation as previously described. The subsystems 10A-10N function in the open loop mode as previously described.

The primary operating difference is that the N subsystems containing an unknown drug dosage form and operating open loop are controlled simultaneously by the identical control signals being generated by the control processor 56 responsive to the output measurements made on the reference dissolution cell, as compared to- the reference drug in vivo dissolution profile. Thus, the in vivo dissolution profile being outputted by the recorder 94A as a time series of known date, in combination with a time series of control signal values produced by the central

processor 56 serves as an Internal Standard in the sense that the predictive profiles are produced in the open loo mode by signals which are simultaneously being produced b closed loop mode of operation using a reference drug and data as the basis. A cursory review of the operation of the basic embodiment of Figure 1, as compared with that o Figure 4, will reconfirm that only comparatively minor- differences in operation of the subsystems are involved. For example, the subsystems 10A-10N have no need to perform the measurement of flow rate and drug concentration in their output lines. Only the subsystem 10R requires that information. In the interest of the uniformity of apparatus, and as a means of providing additional versatility to the Internal Standard system 100, any or all of the subsystems 10A-10N may include the components required to measure these output parameters an provide related signals to the central processor 56. In this latter case, the central processor 56 is merely instructed to ignore the specific output data produced by those particular subsystems which are to be operated open loop.

Summarizing, the Internal Standard embodiment of Figure 4 includes the signal processing elements (the central processor 56 and peripherals group 94) of Figure 1, along with a plurality of the measuring blocks 96 of Figure 1. Of the number of measuring blocks, one (subsystem 10R) serves as a reference subsystem and operates in a closed loop mode with the signal processing elements, while the remainder (subsystems 10A to ION) are controlled by the signal processing elements in the open loop mode. Thus, the plurality of subsystems 10A-10N eac produce a predictive dissolution profile of a separate drug dosage form while all are referenced to a single reference drug dosage form.

Referring now to Figure 5, ther is shown a block diagram of an improved control system for use with the dissolution testing system 10. The improved control system 200 inserts an optimally adaptive capability into the dissolution testing process via a random input modeling (RIM) mode of operation. Briefly, this mode impacts on operation in the closed loop mode wherein the average in vivo human drug response profile A(t), for a reference drug product is reproduced by the concentration va. time profile, C(t), output from the apparatus through feedback control of one or more of the process variables controlling the conditions of the dissolution testing. Random input modeling is performed to tune a PID controller for each process variable and accomplish on-line, optimally adaptive control. These process variables may include the composition (e.g., pH) of the dissolution medium; agitation via stirring paddles; agitation via primary flow rate; and/or sink conditions in the form of recycle flow of medium back into the dissolution cell.

The improved control system 200 may be considered as an expanded version of the closed loop control system shown in more generalized form in FIG. 2. In FIG. 5, the improved control system 200 is shown as a four channel device wherein each channel corresponds to a particular process variable to be optimized. Thus, four proportional-integral-derivative (PID) controllers 202, 204, 206 and 208 have as their common inputs an error signal E(t) derived as the difference between the input signal A(t) and the output signal C(t). Each PID controller also has an individual set of adjust lines taken from the group of parameter adjust lines 210. While the improved control system 200 is clearly shown as being a digital embodiment, the specific apparatus used to implement the controlling has been deemphasized - except

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for a few places where digital-to-analog (D/A) and analog-to-digital (A/D) converters are needed - in order to better clarify the RIM technique which is the heart of the improvement being described. The particular parameters adjusted via the lines 210 are described below Individual outputs from the four PID controllers are routed to a corresponding number of summing junctions 212 214, 216 and 218, respectively; each summing junction als having a pseudo-random binary signal (PRBS) applied to it from a PRBS generator 220, via a four section low pass filter 220A. Individual outputs from the four summing junctions are routed to a corresponding number of D/A converters 222, 224, 226 and 228; and are further routed via a group of lines 230 to other control elements within the parameter adjust section. A set of individual analog control signals from the four D/A's are then applied to a corresponding number of actuators 232, 234, 236 and 238 - which correspond to the various pumps/motors described in connection with FIG. 1. The correspondence is^' as follows: the pH actuator 232 may correspond to the pump 38 and its associated modulator; the agitation actuator 234 may correspond to the stirring paddle 80 and its associated motor; the primary flow actuator 236 may correspond to the primary pump 18 and its associated modulator; and the recycle actuator 238 may correspond to the recycle pump 26 and its associated modulator. The four actuators function, as previously described, to control the process variables establishing the conditions of the dissolution testing resulting in an output concentration of the drug form detected by a spectrophotometer 242 (corresponding to the element 58 of FIG. 1). The concentration vs time profile C(t) - the desired output quantity - is digitized in an A/D converte 244 and is applied first via a path 246 to an input node 248 where it is differenced with the A(t) signals; and further via a path 250 to the inputs of four process variable tuners 252, 254, 256 and 258. The tuners are substantially identical and hence the structure and function of one only will be described. The tuners may be implemented as a discrete collection of digital circuits operating under the control of a central processor (element 56 of FIG. 1); and may also be implemented via separate, but cooperting microprocessors; and may further be embedded in the central processor 56 itself. Tuner 258, the one associated with optimizing the recycle flow rate R(t), is shown as comprised of a cross-correlator 260 to which is applied a pair of input signals on the lines 230A and 250A. The path 250A provides the C(t) signal, while the path 230A provides a combined signal containing the control signal plus the random signal - from the output of summing junction 218. The output from the cross-correlator is integrated in integrator 262, whose output is in turn applied to recycle curve element 264 which produces a process reaction curve directed to optimizing the recycle flow rate parameter. A control parameter determining element 266 receives the output from the recycle curve element 264 and periodically produces updated values for three key parameters, which are applied via an interfacing element 268, for use in the PID controller 208. These three key parameters are the overall controller gain K_f-,; the integral time T_j ; and the delay time T_D- The interested reader is referred to a 1953 published article wherein the parameter-tuning technique of the present invention is described. See, Cohen, G.H. and Coon, G.A. , "Theorectical Considerations of Retarded Control," Trans. ASME, Vol. 74, 1953, pp. 827. The technique has become very well known in the control system arts and is referred to hereinafter as the "Cohen-Coon method".

>t ' In order to improve the fidelity of the bioavailability prediction when the improved control sytems 200 is operating in the open loop mode, it is useful to first determine the proper control parameter {K_Q I TJ and T_D) settings for each of the PID controllers 202, 204, 206 and 208. This is best done by random input modeling during an experimental run performe with a reference drug form in the closed loop mode of operation. The recycle rate control channel is illustrative of the method used. Superimposed on each channel control signal is a pseudo-random binary signal with an amplitude at least one standard deviation greater than the noise level in the channel and a bandwidth corresponding to ten times the bandwidth of the channel. Active electronic filtering of the output from the PRBS generator 220 by a low pass filter 220A may or may not be necessary due the possibility of autofiltering by the mechanical damping characteristics of the activators used. The signal output of the spectrophotometer 240 will contain the results of the control signal plus the PRBS. This signal C(t) is cross-correlated with the combined input signal (control signal plus PRBS) over a period of (illustratively) five time constants to yield a weighting function at the output of the cross-correlator 260. A process reaction curve is produced by integrating the weighting function in the integrator 262, and the control parameters (K_c, T_j and T_D) are determined by the method of Cohen and Cool within the element 266. These new controller settings for each process variable are substituted into the four PID controllers and the process is repeated for another five time constants. The procedure is performed independently for each of the four PID controllers and simultaneously for all four controllers during each experimental run.

This process of controller tuning is initially performed independently (and/or in combination with one or more _.of the other process variables) for each process variable to obtain initial estimates of controller settings for each controller. In the course of an actual run, the controllers for each of the four process variables operate together in parallel and are retuned periodically (every 5 time constants, illustratively) simultaneously to provide hew updated values for the controller settings. Controller setting values obtained by this adaptive control procedure during the course of an experimental run are rejected, and previous values retained, if the proposed values are outside of a range of values for each setting which has been found to induce instability in the operation of one or more of the actuators.

Although the invention has been described in terms of selected preferred embodiments and improvements to these embodiments, the invention should not be deemed limited thereto, since other embodiments and modifications will readily occur to one skilled in the art. It is therefore to be understood that the appended claims are intended to cover all such modifications as fall within the true spirit and scope of the invention.

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Claims

WHAT IS CLAIMED IS:

1. Apparatus for the automated dissolution testing of products whose solubility and dissolution rate properties affect product performance comprising: a) a dissolution cell having an input line, an output line, a filtering chamber therebetween, and controllable agitation means responsive to an agitation control signal, positioned within said chamber; b) at least two reservoirs connected to said input line through a like number of media supply lines fo providing dissolution media from said reservoirs to said filtering chamber; c) first flow control means responsive to a first control signal and positioned in said input line fo controlling the flow of dissolution media through said filtering chamber, and second flow control means responsive to a second control signal and positioned in a least one of said media supply lines for controlling the flow of dissolution media to said input line; d) recirculating means including third flow control means responsive to a third control signal and connected to said input and output lines for controlling recirculatory flow therebetween; e) system output means connected to said outpu line and containing means for measuring output parameters therein including a concentration parameter of particular constituents within said flow, and for providing system output signals corresponding to said measured output parameters; f) memory means for providing stored control signals to said apparatus ; and g) electronic control means connected to said memory means and operative in a first mode responsive to said stored control signals and to said measured output signals for automatically determining a set of internal control parameters used to determine said first, second, and third control signals so as to minimize the differences between said stored and measured signals, and operative in an open loop mode responsive to said determined internal control parameters for automatically producing said first, second, and third control signals in the absence of said stored signals.

2. The apparatus of claim 1 wherein said dissolution cell further comprises: a) agitation means disposed within said filtering chamber and responsive to an agitation signal for controlling the agitation rate within said chamber; and b) wherein said electronic control means further comprises means for producing said agitation signal responsive to said internal control parateters, whereby said first, second and third control signals in combination with said agitation signal serve to minimize the differences between said stored and measured signals .

3. The apparatus of claim 2 wherein said measured output parameters include a flow parameter corresponding to the flow through said system output means .

4. The apparatus of claim 2 wherein said electronic control means includes means for determining a flow parameter corresponding to the flow through said system output means by determining the difference between said first and thrid control signals.

5. The apparatus of claim 2 wherein said at least two reservoirs provide dissolution media of

t :*'. ^τ . substantially different characteristics and said electronic control means includes means for controlling the ratio of said different dissolution media by adjustin the ratio of said first and second control signals.

6. The apparatus of claims 5 wherein said at least two reservoirs contain acidic and alkaline media^" respectively, and said ration of said different dissolution media constitutes a pH control.

7. The apparatus of claim 6 wherein said product is a pharmaceutical drug dosage form and said stored control signals comprise in vivo dissolution profiles.

8. A method of automatic dissolution testing of products whose solubility and dissolution rate properties affect product performance having unknown dissolution profiles by comparison, against known product forms having known dissolution profiles, comprising: a) flowing a dissolution medium of controllabl content at a controlled flow rate through a dissolution cell containing said known product form; b) providing a recirculation path around said dissolution cell to provide controllable sink conditions therethrough; c) measuring the concentration profile of said known product form at the output of said dissolution cell and providing output signals corresponding thereto;. d) providing stored signals corresponding to the concentration profile of said known product form; e) producing a first family of control signals such that the differences between said stored signal and said output signals are minimized;

~ f) producing a second family of control signals for controlling said medium controlled content, said controlled flow rate, and said controlled sink conditions from said first family of control signals; and g) flowing a dissolution medium of said controlled content at said controlled flow rate through a dissolution cell containing said unknown product form_ whereby measured concentration profiles of said unknown produce form are derived as being predictive of subsequent usage dissolution profiles.

9. The method of claim 8 further comprising the step of providing agitation at a controllable rate within said dissolution cell and wherein said second family of control signals includes signals for controlling said controllable agitation rate.

10. The method of claim 9 wherein said step of flowing a dissolution medium of controllable content comprises controlling the pH of said controlled medium.

11. The method of claim 9 wherein said stored signals comprise a time series representative of said concentration profile over a predetermined period of time.

12. The method of claim 9 wherein said first family of control signals comprises a set of overall control parameters for controlling said dissolution testing process and said second family of control signals comprise a set of process variables for controlling said controlled content, flow rate, sink conditions and agitation rate.

13. The method of claim 9 wherein said produc is a pharmaceutical drug dosage form and said stored signals comprise in vivo dissolution profiles and said predictive subsequent usage dissolution profiles comprise predictive in vivo dissolution profiles.

14. A method of simultaneously predicting in vivo dissolution profiles of a plurality of pharmaceutical drug dosage form by comparison with a reference drug dosage form having a known in vivo dissolution profile, comprising: a) passing a reference dissolution mediumformulated as a mixture of at least two constituents under the control of a mixture control signal through a reference dissolution cell containing said reference drug, at a flow rate controled by a flow control signal and at an agitation rate within said dissolution cell controlled by an agitatio control signal; b) flowing a plurality of dissolution media, eachof which is formulated as a mixture of at least two constituents under the control of said mixture control signal, through a corresponding plurality of dissolution cells,_, each of which contains a different one of said plurality of drug dosage forms; c) providing a separate recirculation path around each of said dissolution cells, each ath having a recirculation rate controlled responsive to a sink control signal; d) measuring the concentration profile of said reference drug at the output of said reference dissolution cell and providing a time series of output signals corresponding thereto; e) providing a time series of stored signals corresponding to the concentration profile of said reference drug;

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f) producing a set of optimized process variable control signals optimized by deriving a difference signal between said time series of output signals and said time series of stored signals; and g) producing said mixture control signal, said flow control signal, said sink control signal and said agitation control signal such that said derived difference signal is continually minimized.

15. The method of claim 14 further comprising the step of introducing a pseudo random binary signal into a processed version of said derived difference signal to further optimize in part said optimized process variable control signals .

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