Irradiation Chamber for Photoactivation Patient Treatment System

This invention relates to the field of treating cells with photoactivatable compounds and radiation which activates the compound thereby affecting the cells and specifically, relates to clinically useful systems for the extracorporeal treatment of blood cells, especially leukocytes, including a disposable source of U.V. radiation in a removable light array assembly.

BACKGROUND OF THE INVENTION

It is well-known that a number of human disease states may be characterized by the overproduction of certain types of leukocytes, including lymphocytes, in comparison to other populations of cells which normally comprise whole blood. Excessive or abnormal lymphocyte populations result in numerous adverse effects to patients including the functional impairment of bodily organs, leukocyte mediated autoimmune diseases and leukemia related disorders many of which often ultimately result in fatality.

U.S. Pat. Nos. 4,321,919; 4,398,906; 4,428,744; and 4,464,166 to Edelson describe methods for treating blood whereby the operation or viability of certain cellular populations may be moderated thereby providing relief for these patients. In general, the methods comprise treating the blood with a dissolved photoactivatable drug, such as psoralen, which is capable of forming photoadducts with DNA in the presence of U.V. radiation. It is believed that covalent bonding results between the psoralen and the lymphocyte nucleic acid thereby effecting metabolic inhibition of the thusly treated cells. Following extracorporeal radiation, the cells are returned to the patient where they are though to be cleared by natural processes but at an accelerated pace believed attributable to disruption of membrane integrity, alteration of DNA within the cell, or the like conditions often associated with substantial loss of cellular effectiveness or viability.

Although a number of photoactivatable compounds in the psoralen class are known, 8-methoxy psoralen is presently the compound of choice. An effective radiation for this compound, and many psoralens in general, is the ultraviolet spectrum in the range of approximately 320 to 400 nanometers, alternatively referred to as the U.V.A. spectrum. As the development of photoactivatable compounds proceeds, it may be expected that changes in the preferred activation radiation spectrum will be necessary. Suitable selection of radiation sources will, of course, increase treatment efficiency and is contemplated as an obvious optimization procedure for use with the inventions disclosed herein.

Although Edelson's methods have been experimentally shown to provide great relief to patients suffering from leukocyte mediated diseases, numerous practical problems require solutions. In particular, Edelson fails to provide a suitable apparatus for applying radiation to the cells, e.g. via a treatment station, in an economical and efficacious manner, or a system for incorporating a treatment station providing for the treatment of a patient in a clinically acceptable format.

Conventional techniques for photoactivating compounds associated with cells have relied on a plurality of devices including flasks, filtration columns, spectrophotometer cuvettes, and petri dishes. The sample to be irradiated is added to the containers and the container placed adjacent to the radiation source. Such systems tend to be laboratory curiosities as they fail to provide the necessary safeguards intrinsically necessary where patient bodily fluids are concerned, particularly since these fluids must be returned to the patient thereby necessitating strict avoidance of contamination. Further, such methods tend to be volume limited, are characterized by many mechanical manipulations and are generally unacceptable from a clinical and regulatory viewpoint. It is an object of the present invention to provide methods and apparatus suitable for use with the Edelson methods to overcome the limitations associated with the conventional expedients.

Copending applications U.S. Ser. No. 650,602, now abandoned describes a practical device for coupling the radiation provided by commercially available light sources, such as the so-called "black-light" fluorescent tubes, to cells for treatment by Edelson's photoactivated drug methods. In summary, the disposable cassette described therein comprises a plurality of fluorescent tube-like light sources such as the U.V.A. emitting Sylvania F8TS/BLB bulb, which are individually, coaxially mounted in tubes of larger diameter which are, in turn, coaxially mounted in sealing arrangement within second outer tubes of even larger diameter thereby forming a structure having two generally elongated, cylindrical cavities about each radiation source. The inner cavity preferably communicates with the atmosphere thereby facilitating cooling of the radiation source. The second tube forming the outer cavity further comprises inlet and outlet means for receiving and discharging, respectively, the cells to be irradiated. A plurality of these structures are "ganged" and suitable connections made between inlets and outlets of adjacent members to provide for serpentine flow of cells through each outer cavity. Thus, continuous flow of the cells through the plurality of cavities surrounding the centrally disposed radiation sources facilitates thorough treatment of the cells. Additional, detailed description of the Taylor device may be obtained by direct reference to U.S. Ser. No. 650,602 now abandoned.

To be fully practical, the Taylor device requires a clinically acceptable instrument to house the device and to provide the cells to be treated in an appropriate form. Such an instrument is the object of the inventions described in U.S. Pat. Nos. 4,573,960, 4,568,328, 4,578,056, 4,573,961, 4,596,547, 4,623,328 and 4,573,962, fully incorporated herein by reference. While the instruments described therein work well, it is an object of the instant application to describe improved systems capable of implementations, in advanced fashions, the medical treatment principles first taught by Edelson.

It is another object of the present invention to provide still further improvements in greater patient safety and comfort while reducing treatment time and coast, by utilizing a newly designed disposable irradiation chamber in an appropriate instrument which incorporates a new, advanced photoactivating light array assembly.

It is yet another object to provide an improved instrument which meets the above criteria while maintaining the positive attributes of the prior system; compactness, mobility, completeness, fully automated and monitored, coupled with ease of operation.

It is a further related object of this invention to provide, in contrast to the time consuming batch like processing of the prior system, disposable light array assembly for use with a continuous on-line patient treatment system wherein collection, separation, and cell treatment occur simultaneously, thereby reducing treatment time and increasing patient safety and comfort.

These and still other objects of the invention will become apparent upon study of the accompanying drawings wherein:

FIG. 1 illustrates a preferred configuration of the system during collection, separation, and treatment;

FIG. 2 shows a front elevational view of the flat plate irradiation chamber mating with a recirculation pump; and photoactivating light source array;

FIG. 3 shows a bottom view of the preferred embodiment of the light array assembly with the irradiation chamber mounted therein;

FIG. 4 shows a perspective view of the most preferred embodiment of the irradiation chamber; and

FIG. 5 shows a side view of the FIG. 4 embodiment.

In accordance with the principles and objects of the present invention there is provided a disposable irradiation chamber for use with a patient treatment apparatus. The patient treatment system provides for "on-line" extracorporeal photoactivation of a photoactivatable agent in contact with patient cells, particularly blood, by collecting and separating blood on a continuous basis, returning to the patient undesired blood portions obtained during separation while the desired portion is photoactivatably treated and thereafter returning the thusly treated cells to the patient. As a result of this novel approach, the treatment system of the instant inventions optimizes and minimizes treatment time by concurrently conducting various aspects of a photoactivation treatment process which were previously performed sequentially.

More specifically, the apparatus collects and separates blood on a continuous basis as it is withdrawn from the patient and returns unwanted portions to the patient while concurrently energizing the photoactivating irradiation sources in a disposable light array assembly. The energized light assay photoactivates the photoactivatable agent in contact with the desired blood portion while the agent and the cells (or other patient fluid) is contained within the flat plate irradiation chamber of the chamber-pump block of the instant invention. Following photoactivation, the treated cells may then be facilely returned to the patient utilizing a drip chamber gravity feed infusion line incorporated in a dedicated tubing set.

The irradiation chamber of the instant invention provides for efficient activation of photoactivatable agents by irradiation from light array assembly described U.S. Ser. No. 834,256. In the most preferred embodiment, irradiation of both sides of the irradiation chamber takes place concurrently while still permitting facile removal of the chamber. A most preferred embodiment of the chamber further comprises a solid state device for controlling the use of the irradiation chamber thereby ensuring patient safety and device efficacy.

FIG. 1 shows various aspects of the system developed for extracorporeally treating a patient based in part upon the scientific discoveries of Edelson. While the specific design, construction and operation of the apparatus 10 is the result of a number of separate inventions some of which form the subject matter of previously described issued patents and copending commonly assigned applications including U.S. Ser. No. 834,292 entitled "Concurrent On-Line Irradiation Treatment Process"; U.S. Ser. No. 834,293 entitled "Electronic Device For Authenticating and Verifying Disposable Elements"; U.S. Ser. No. 834,294 entitled "Disposable Temperature Probe For Photoactivation Patient Treatment System"; U.S. Ser. No. 834,303 entitled "Improved Valve Apparatus For Photoactivation Patient Treatment System"; U.S. Ser. No. 834,256 entitled "Light Array Assembly For Photoactivation Patient Treatment System"; U.S. Ser. No. 834,257 entitled "Pump Block For Interfacing Irradiation Chamber To Photoactivation Patient Treatment System"; U.S. Ser. No. 834,260 entitled "Demountable Peristaltic Pump For Photoactivation Patient Treatment System"; and U.S. Ser. No. 834,259 entitled "Zero Insertion Force Socket For Photoactivation Patient Treatment System"; the relevant parts of which are fully incorporated herein by reference, it is believed a brief description may be helpful.

The operation of the device and performance of the methods can be divided into two basic phases or modes, depicted in part by FIG. 1. The first phase is shown substantially in FIG. 1 wherein the patient is connected at the point shown, preferably by venipuncture or the like methods well-known and developed to a high degree in the dialysis arts. Patient blood, as it flows to the apparatus 10 (alternately referred to herein as the puvapheresis apparatus or system) is preferably infused, under control of pump 11, with an anticoagulant agent contained in container 20 hung from stand 15. Control of the flow of patient blood to the remainder of apparatus 10 is controlled largely by clamping means 16a which has the dual function of also controlling flow in the reverse direction as well as flow to return container 21. Clamp 16a acts as an "or" valve.

Normally the blood flows through tubing 24 through blood pump 12 (preferably a roller pump such as that described in U.S. Pat. No. 4,487,558 to Troutner entitled "Improved Peristaltic Pump" and incorporated herein by reference) into continuous centrifuge 13. This continuous centrifuge, available commercially from suppliers such as Dideco, Haemonetics and others, is preferably capable of continuously separating blood based on the differing densities of the individual blood components. "Continuously", as used herein means that, as blood flows into the centrifuge through line 24, it accumulates within the rotating centrifuge bowl and is separated so that low density components are emitted after a certain minimum volume has been reached within the centrifuge bowl and as additional blood is added. Thus, the continuous centrifuge in effect acts as a hybrid between a pure on line system and a pure batch system. This occurs because the centrifuge bowl has a capacity to hold most, if not all, of the most dense portion, typically erythrocytes or red blood cells while emitting lower density portions such as plasma and leukocytes (white blood cells) as whole blood is continuously added. At some point, however, the reservoir volume of the centrifuge is filled with the higher density components and further separation cannot be effectively obtained. Prior to that point, the operator, by viewing the uppermost portion of the centrifuge bowl through the centrifuge cover, can detect qualitatively when the centrifuge emits plasma (as opposed to priming solution), leukocyte enriched portions and the remainder, i.e., nonleukocyte enriched portions, including erythrocyte enriched portions. Based on the operator's observations, he or she enters through control panel 19 (specifically via panel portion 42) the identification of the individual blood portions as they are emitted from the centrifuge. This information is entered by keys 44 (e.g., PLASMA, BUFFY COAT or leukocyte enriched portion) on control panel 19, and in response thereto, the apparatus 10 controls valve mechanism 16c to direct the leukocyte enriched portion and a predetermined volume of plasma into plasma-leukocyte enriched container 22 while excess plasma, air, priming fluids, erythrocytes etc. are directed to container 21.

Once the centrifuge is no longer capable of further separation due to the attainment of its capacity, the operator directs that the bowl be emptied by suitable data key entry on panel 19 and the fluid contents of centrifuge 13 are advantageously pumped into return container 21 by means of pump 12 under the control of valves 16a and c. The foregoing steps may be repeated a number of times or cycles before the desired volume of leukocyte enriched blood and plasma is obtained for further treatment, in each instance the undesired portions being collected in return container 21.

Between cycles, the fluids, including erythrocytes which have been pumped into return bag 21 are gravity fed back to the patient through a drip infusion operation and controlled by valve 16b. It is preferred that gravity feed be employed rather than pumping the blood back to the patient via pump 12 in order to avoid potential pressurization problems at the infusion insertion site at the patient, and also to avoid foaming or other air related dangers.

As may be already appreciated, when initially set up, the centrifuge bowl and line 24 may be expected to contain sterilized air which is preferably removed by suitable priming operations advantageously accomplished by utilizing the anticoagulation agent in container 20; both the air and a portion of priming solution being collected in container 21.

Also to be noted is the predetermination of the desired leukocyte enriched volumes and plasma volume to be collected within container 22 as well as the number of cycles to be employed to collect same. These volumes are selected largely in accordance with the individual volume capacities of the containers as well as the treatment chamber to be described later. Accordingly, these volumes are set in order to preferably optimize handling efficiency and to ensure patient safety. For instance, one preferred selection would include the following settings: 250 ml total buffy coat or leukocyte enriched portion and 300 ml of plasma to be collected within container 22. This might require any number of cycles, preferably on the order of three or four, bearing in mind that the more cycles that are selected, the lower the total volume of blood withdrawn from the patient at any one time. If blood collection meets the minimum capacity limits of the centrifuge bowl, the patient's capacity to withstand temporary blood volume depletions and the treatment procedure in general is increased. Further, more cycles will permit more discriminating selection of leukocyte enriched blood as it is emitted from the centrifuge. The buffy coat and plasma volumes as well as the number of cycles are typically physician selected. Accordingly, the controls governing these selections are preferably placed within the apparatus 10, such as behind door 18a where their inadvertent alteration may be advantageously avoided, especially since no operator interaction is normally required with respect to these data inputs.

The leukocyte enriched container 22 is connected via tubing line 34 to the flat plate treatment irradiation chamber behind assembly door 17 with a return line 35 to reservoir container 22.

Referring now to FIG. 2, the leukocyte enriched blood, plasma, and priming solution contained in reservoir 22 (FIG. 1) is delivered through line 501 to the inlet 209 of the flat plate irradiator 513. The cavity in the flat plate is relatively "thin" (e.g. on the order of approximately 0.04") in order to present large surface area of leukocyte rich blood to irradiation and reduce the self-shielding effects encountered with lower surface area/volume ratios. The fluid flows upward through the serpentine pathway in cavity 503 in the irradiation chamber to the outlet 210. While a serpentine pathway is preferred in order to avoid or minimize stagnant areas of flow, other arrangements are contemplated. Outlet tubing 511 passes through the pump block 504 [described in greater detail in U.S. Ser. No. 834,257], affixed to the end of the flat plate irradiator 513, and then connects to return line 35 which returns fluids from the irradiation chamber to container 22.

Recirculation pump rotor 203, which is located internally in the machine (mounting not shown), engages the tubing in the pump block in the semi-circular tract 508 and thereby provides and controls the recirculating flow of fluid, from container 22 up through irradiation chamber 513 and back to container 22. In a preferred embodiment, a metal segment 220 in outlet tubing line 511 incorporates a thermocouple 213 [described more fully in U.S. Ser. No. 834,294] which permits monitoring of the fluid temperature.

Sterile air initially contained in the irradiation chamber cavity 503 is displaced by entering fluid and stored in the top of container 22. By reversing the rotation of recirculation pump rotor 203, the air stored in container 22 can be pumped back into the outlet 210 of the chamber 513 thereby displacing all fluids back into container 22. Once fluid is initially delivered to container 22, the recirculation pump rotor 203 is energized filling the irradiation cavity 503 and displacing sterile air to container 22. When the irradiation chamber is filled and BUFFY COAT button 44 on panel 19 is pressed, the light array assembly which surrounds the irradiation chamber is energized. Continued operation of the recirculation pump rotor 203 continuously recirculates the leukocyte enriched fluid from container 22 through the chamber for receiving photoactivating radiation from the energized light array assembly 401 (FIG. 3) and back to container 22.

FIG. 3, illustrating the light array assembly 401 from a bottom view, shows two rows, in the most preferred embodiment although one row can be used, of radiation sources 400 powered through contacts 216. Such sources are conveniently chosen so that illumination is reasonably constant over the entire irradiation cavity 503 (FIG. 2). Suitable sources include the Sylvania FR15"T8/350BL/HO/180.degree. with 2011 phosphorus bulb which is in the so-called fluorescent tube form. As is apparent from FIG. 3, the irradiation chamber 513 slides between the rows of radiation source 400 so that pump block 504 engages pump rotor 203 driven by motor 250. Other aspects of the light array assembly 400 are discussed in U.S. Ser. No. 834,256.

Thus, photoactivation of the leukocyte enriched fluid by irradiation is initiated at the outset of, and continues during and after the collection and separation process. In the most preferred mode, the light array assembly will comprise sources of ultraviolet radiation, most preferably of the UVA type for activating the photoactivatable agent presently of choice, 8-methoxy psoralen.

In operation, and with respect to FIG. 1, the exposure time on the right hand portion of the panel 19 is set in accordance with physician determined criteria. The central control means of the apparatus 10, calculates and displays on one section of the panel 19, via central processing unit and memory stored software, the exposure time remaining at the onset of irradiation treatment and as the treatment progresses. Another section of the control panel also includes three operator controlled entry data keys whereby the operator can de-energize the light assembly array and stop the recirculation process if desired. Actual photoirradiation treatment preferably commences automatically under control of the central processing unit when fluid is first directed to container 22, continues while leukocyte enriched blood portion from container 22 is pumped through the irradiation chamber back into container 22, and terminates when the present exposure time has expired. At that time, the light array assembly is de-energized and the recirculation pump reverses emptying the contents of the irradiation chamber 513 into container 22.

Thereafter container 22 is ideally removed to stand 15 where it is connected to tube 36, provided on the common drip chamber 21a also associated with return container 21, for reinfustion of the treated blood portion into the patient.

To enhance patient safety and decrease the risk of contamination to the patient blood and blood portions, each time a connection is made or broken, it is preferably only done once. Thus, container 22 would ideally have four connection points or ports; one for the collection of the leukocyte enriched blood portion, two for connection to the flat plate irradiation chamber (feed and return), and the fourth for connection to the drip chamber (21a) for reinfustion of treated blood to the patient.

With further reference to FIG. 1, the control panel 19 of the apparatus 10 is shown with the keyboard entry buttons 44, each ideally having a light which, when lit, preferably indicates the stage of the operation. Advantageously, the keyboard entry buttons 44 are preferably placed in sequential order thereby assisting the operator in learning the system and performing the steps in the correct order. Indeed, the central control means will preferably be programmed to prevent out of step sequences from being implemented. A visual display indicates the volume of leukocyte enriched blood collected in container 22.

Panel 19 will preferably also contain a power switch, as well as a blood pump speed control whereby the operator may select the speed with which the blood is withdrawn from the patient and pumped through the system during collection. Also preferably included is an alpha-numeric display for indicating the machine's status and identifying alarm conditions throughout system operation. Optional accessory status lights, preferably provided in green, yellow, and red colors, provide at a glance the overall operating status of apparatus 10. Further included is a mute/reset button for quieting an audible alarm activated in the event an alarm condition occurs and operator input is required.

Other features may be readily apparent from the drawings such as the preferable inclusion of casters and caster brakes for enhancing the mobility of the apparatus. Further, side panel 23 will preferably include mechanical means (e.g. hanging pegs and the like) for assisting in the securement of container 22. It may also optionally be outfitted with a transparent or translucent opening 18b in the area beneath container 22 for providing at a glance information regarding the illumination status of the irradiation treatment chamber during the treatment phase. For instance, if the window is of sufficient size, the operator may readily determine that each irradiation source within the treatment chamber is illuminated as desired. Naturally, the material comprising such window is preferably selected in order to contain harmful radiation, if any, within apparatus 10.

The aforedescribed photopheresis blood treatment apparatus is made largely possible by an automated control method for directing the blood portions, derived from the continuous centrifuge, into particular containers. The automated method performs in accordance with preset volume determinations which are manually entered behind panel 18a pursuant to a physician's direction. These predetermined volumes specify the volume to be contained within container 22 by setting forth the volume of plasma and the volume of leukocyte enriched blood portion to be directed thereto. Additionally included within these condition setting parameters is preferably the ability to set forth the number of cycles of blood collection and separation required or desired in order to obtain the desired blood volumes.

The volumes collected are determined in accordance with the blood volume pumped by the blood pump. This may be suitably monitored and communicated to the central control means by specifically monitoring the number of step pulses input to the pump to cause rotations of the blood pump. Typically, 200 pulses results in one revolution. Rotation may also be conveniently monitored such as by attachment of a slotted disk to the shaft and the passage of slots determined by an optical sensor means such as that described in U.S. Pat. No. 4,623,328 (fully incorporated herein) and by monitoring shaft rotation. The resultant periodic signal may be conveniently correlated with speed and number of rotations by circuit designs well-known in the art. The number of rotations by any of the foregoing methods coupled "with the known volume pumping characteristics of the pump", will provide the necessary information regarding the volume of blood pumped. It will readily be appreciated that the sensors need not be optical but may be electronic or mechanical instead.

In actual operation, a most preferred procedure would be as follows. The operator presses teh PRIME CENT. key on control panel section 19 which primes the tubing set, the blood pump, and the centrifuge with the anticoagulation solution contained in container 20. Displaced sterile air is collected in container 21. When priming solution emerges from the exit of the centrifuge, the operator presses PRIME U.V. key on control panel section 42 which closes the tubing line to container 21 and opens the tubing line to container 22 by means of valve 16c. Recirculation roller pump rotor 203 is energized to prime the flat plate irradiation chamber and displce sterile air to container 22. The priming process stops automatically after a preset volume of fluid is delivered to container 22.

Blood collection is started by the operator pressing START key on control panel 19. Thereafter, blood is withdrawn from the patient and pumped by the blood pump into the rotating centrifuge. As the blood enters the centrifuge, it displaces the priming solution which emerges first in accordance with its preferably lighter density. This priming solution is automatically directed into container 22 until a preset volume is delivered, after which the emerging solution is redirected to container 21 by means of valve 16c. At some point, the priming solution will be completely displaced from the rotating centrifuge and plasma will begin to emerge. This emergence may be directly observed through port 14 whereupon the operator presses the PLASMA key on control panel 19. Thereafter, the central control means automatically directs the plasma into container 22 by altering valve 16c keeping track of the volume as it does so since the volume entering the centrifuge equals the volume emerging therefrom. This continues until the operator indicates the leukocyte enriched portion, i.e. buffy coat has begun by pressing the respective data entry key in control panel section 42 whereupon, the leukocyte enriched portion continues to container 22, however, the volume so directed is monitored as buffy coat volume. Alternately, if all of the predetermined plasma volume is collected prior to the emergence of the buffy coat, then the central control means automatically diverts, by valve 16c, the emerging plasma fluid stream to container 21. In that instance, upon the emergence of the buffy coat and the keying of the BUFFY COAT data entry switch 44, the central control means diverts the emerging buffy coat into container 22. By means of valve 16c, again keeping track of its volume.

The collection of the buffy coat will preferably continue in accordance with both the predetermined buffy coat volume as well as the number of cycles, another condition predetermined by the physician. If this most preferred embodiment is employed, then a representative example might be as follows. Asume, that the predetermined volume and cycle conditions are set as follows: 350 mls of plasma, 250 mls of buffy coat, and 5 cycles. In each cycle, the apparatus will collect 250/5 or 50 mls of buffy coat before ending the cycle and thereupon emptying the centrifuge bowl and returning all nonleukocyte fluids, predominantly etythrocytes and perhaps excess plasma, to the patient. Prior to the collection of the 50 mls, plasma will emerge from the centrifuge and will be collected in container 22 either until the full 350 mls are collected or, until the buffy coat emerges.

During the next cycle, the central control means will direct the further collection of plasma, if needed, in order to reach the 350 ml predetermined volume and then collect an additional 50 mls of buffy coat. The total volume to be contained within container 22, will then equal 600 mls and would be indicated on display 46 as it is accumulated.

Thus, the instant invention serves to automatically keep track of the volumes as they are collected thereby facilitating the institution of a convenient number of cycles whereby the removal of large blood volumes from the patient is avoided. Not only is patient safety enhanced thereby, but the automated nature of the procedure further increases safety since, in accordance with the programmed conditions supplied to the central control means, the operator need not attempt to keep track of plasma and leukocyte enriched volumes collected, while still being assured that the final solution for treatment will contain the predetermined and desirable leukocyte concentration.

The foregoing described automated methods used in the photopheresis apparatus described with respect to FIG. 1 advantageously employ the instant invention, in particular a removable and disposable irradiation chamber-pump block for containing the patient fluids/cells and photoactivatable agent for exposure to photoactivating radiation from the light array assembly.

With specific reference to FIGS. 4 and 5, the most preferred arrangement of the irradiation chamber-pump block combination is shown. Irradiation chamber 513 comprises a serpentine pathway 503 for conducting patient fluid from inlet line 501 and presenting the patient fluid in a physical arrangement having a large surface area to volume ratio. Thus, self-shielding effects of the cells is reduced while the cells are photoactivated by irradiation impinging upon both sides of serpentine portion 512 by the light array assembly. After photoactivation, the fluid leaves pathway 503, enters outlet tube 511 which is threaded through pump block 504 along arcuate pump race portion 508 and outlet 502. Arcuate pump race 508 engages a roller pump mechanism (see FIG. 2) for creating peristaltic flow through inlet 501, pathway 503, and outlet 502. Shoulder means 509 prevent creep of outlet tubing 502 during pumping action. Slots 507 are provided for engagement with assistance levers associated with the patient treatment system. The assistance levers are activated by the treatment system's central control processor for urging the irradiation chamber 513, and more particularly, the arcuate pump race 508 of pump block 504 against the compressive forces exerted by the rollers of pump 203 (see FIG. 2). During such engagement, electrical contact is made between the treatment system and temperature probe 213 [more fully described in U.S. Ser. No. 834,294], and finger contacts 505 electrically connected to electronic memory device 506.

The serpentine pathway portion 512 is preferably formed by bonding together in sealing arrangement male and female thin plate sections. Such sections are preferably comprised of a material ideally transparent to the wavelength of photoactivating radiation. In the case of ultraviolet A radiation, polycarbonate has been found most preferred although other materials may be employed. Similarly, many known methods of bonding may be employed and need not be expanded on here. The irradiation chamber 513 optionally comprises periodic protrusions within the track holding outlet tubing 502 for restraining same in secure fashion. Pump block 504 may be molded as part of the serpentine pathway section 512 or optionally out of separate materials and subsequently mounted to section 512 as convenient.

In the most preferred embodiment and as additionally described in copending patent application Ser. No. 834,293, fully incorporated herein by reference, a integrated circuit memory device 506 is installed on a circuit board affixed to chamber 513 for retaining encoded information specific for the particular chamber such as type, serial number, certification number, manufacturing site, and, if applicable, prior usage. the memory device is electronically connected to the central control processor of the patient system by finger contacts 506 which electrically engage contact sockets (not shown) described more fully in U.S. Ser. No. 834,259.

As may be apparent, numerous advantages are obtained by the present invention. The irradiation chamber-pump block combination comprises a rigid and easily handled assembly requiring no additional structural elements thus providing maximum ease of handling and assembly at minimum costs. The chamber can be installed in one simple plug-in step thereby facilitating treatment by less trained personnel particularly since fluid connections are easily made and procedures for routing tubing lines through peristaltic pumps are obviated. The thickness of the irradiation chamber will ideally be determined in accordance with the strength of the photoactivating radiation, a predetermined level of photoactivating efficiency based on the type and concentration of the drug, and the patient fluid to be treated. Advantageously, the incorporated memory device provides information for the central control processor of the apparatus to determine authenticity and suitability of the chamber for use thereby assuring patient safety. The memory device can also identify variations in the type of treatment to be effected based on the fluids to be treated.

Upon study of the accompanying figures, and the foregoing description, it will become readily apparent to the skilled artisan that numerous alternatives may be made to the foregoing such as different number or width of pathways in the chamber, or utilizing a different mechanical configuration of the pump block, etc. without departing from either the spirit or scope of the instant invention.