CA2211848C - Peritoneal dialysis apparatus - Google Patents

Abstract

An automated peritoneal dialysis machine is provided which is capable of selecting and changing the composition of dialysate delivered to a patient in the course of treatment to meet specific physiological needs.
The apparatus includes means for metering solutions of osmotic agent, electrolytes and other desired dialysate components from separate solution containers into mixing chamber means for combination in desired proportions.
The means for delivery of fresh dialysis fluid to a patient and for removing spent dialysis fluid from the patient includes means for monitoring intraperitoneal pressure and other conditions of the fluid in the peritoneum and electronic control means responsible to the signal of monitoring means for controlling rates of dialysate infusion and removal.

Description

METHOD AND APPARATUS FOR PERFORMING PERITONEAL DIALYSIS

This invention relates to a new machine and method for carrying out automated peritoneal dialysis (PD).

Background of the Invention Unlike the extracorporeal system used in hemodialysis (HD) to treat end stage renal disease (ESRD), PD makes use of the internal peritoneal membrane to purify the blood of ESRD patients. The two modalities for carrying out PD are automated peritoneal dialysis (APD) and the manual non-automated procedure of continuous ambulatory peritoneal dialysis (CAPD).
According to the latter method, dialysis fluid is exchanged from four to six times throughout the day, every day. The fluid remains inside the patient for about four hours between exchanges and for a much longer period (10-12 hours) at night.

It has become conventional to refer to the basic stages of the PD procedure as FILL, DWELL and DRAIN. In the FILL stage, dialysate is instilled through a catheter into the peritoneal cavity of a patient.

During the fixed time period known as the DWELL, the dialysate draws soluble waste and excess fluid from blood contained in numerous blood vessels of the peritoneal membrane, by the operation of osmosis and diffusion.
Additionally, the dialysate re-balances the electrolyte concentration and corrects for acidosis of the blood.

At the end of the DWELL, spent dialysate is removed from the peritoneal cavity (DRAIN) and discarded. This exchange action must be repeated several times over a twenty-four hour period, as the body continuously produces waste products.

~ . CA 02211848 1998-07-27 Compared with HD, PD is a very gentle modality, its slow corrective action resembling that of the natural kidney. It is operationally simple, eliminates the need for venipunctures and has low operational costs. Because the system is not an extracorporeal one, there is no need for a high degree of heparinization, a factor which is especially important in the case of diabetic patients.

However, to date HD has continued to dominate in the treatment of ESRD patients. The following aspects of PD
may be contributing factors to this state of affairs:

- In PD, the peritoneal membrane is exposed to the external environment every time a catheter is connected or disconnected from the solution supply, making infection (peritonitis) a significant problem.

- Currently available commercial dialysate for PD
exhibits a low pH which is not truly compatible with the biochemistry of the peritoneal membrane.
Consequently this bio-incompatibility is believed to be one of the factors which eventually degrades the performance of the membrane with time.

- The most popular osmotic agent used in PD dialysates is glucose, Glucose can be absorbed by the body via the peritoneum membrane. This can result in patient obesity and its accompanying complications Moreover, heat sterilization of the dialysate which contains glucose produces harmful glucose by-products.

- Current techniques of PD afford no ability to monitor the pressure build-up in the peritoneum during either Dwell or during the Fill sequence.

- Current PD solutions are of fixed composition and cannot be systematically adjusted either in their constituent parts or in the concentration of each constituent during a treatment.

In a continuing effort to provide adequate PD
treatment for the varied population of ESRD pàtients, clinicians have developed a number of different forms of the APD modality of treatment. These include the APD
modalities of:

(i) Continuous Cycling Peritoneal Dialysis (CCPD), a method of performing PD in which an automated cycler performs 4 to 6 regular exchanges every night.

(ii) Intermittent Peritoneal Dialysis (IPD), a method of performing PD in hospitals or at home with an automatic cycler two or three times a week for a period of about eight to twenty hours each time.

(iii) Nightly Peritoneal Dialysis (NPD), a method of performing nightly peritoneal dialysis at home for patients with high efficiency peritoneal membranes. Such patients do not fare well with long dialysate DWELL times.

(iv) Tidal Peritoneal Dialysis (TPD). This modality utilizes an initial maximum dialysate fill volume (usually three litres) and periodically, during a long and continuous DWELL time, drains a fraction of the fill volume (usually one-third, the tidal volume) and re-infuses about a similar amount, adjusting for ultrafiltration (excess fluid removed from the patient's body during kidney dialysis) into the patient.

A number of examples of more or less "automated"
peritoneal dialysis machines are to be found in the art.
Examples are afforded by U.S. Patent No. 4,096,859 (Agarwal et al.); U.S. Patent No. 5,141,492 (Dadson et al.); U.S. Patent No. 5,324,422 (Colleran et al.); and U.S. Patent No. 5,438,510 (Bryant et al.). These have proven to be unsatisfactory in various respects in addressing clinical concerns and in effectively implementing PD modalities such as those described above.

General Description of the Invention Applicant's overall objective was to provide an automated peritoneal dialysis machine capable of fully "customizing" the composition of dialysate delivered to a patient to meet his or her immediate physiological needs and, to that same end, capable of monitoring the effectiveness of treatment during the treatment process and use this diagnostic information to optimise the customisation process.

It is a particular object of the invention to provide an automated peritoneal dialysis apparatus as aforesaid, including means for metering solutions of osmotic agent, electrolytes and other desired dialysate components from separate solution containers into mixing chamber means for combination, in desired proportions, to provide the desired dialysis fluid and for delivering a selected quantity of said dialysis fluid to the peritoneal cavity of a patient.

It is likewise an object of the present invention to provide automated peritoneal dialysis apparatus as aforesaid, wherein said means for metering dialysate components into the mixing chamber and delivering dialysis fluid to the patient includes means for withdrawing spent dialysis fluid from the patient.

- - - - - -It is a still further object of the invention to provide automated peritoneal dialysis apparatus as aforesaid, wherein the means for delivery of fresh dialysis fluid to a patient and for removing spent dialysis fluid from the patient includes means for monitoring interperitoneal pressure and electronic control means responsive to the signal of said pressure monitoring means, for controlling the rates of infusion of fluid into the patient and for the removal of fluid from the patient and, for the customisation of the dialysate.

Brief Description of the Drawings Figure 1 is a schematic representation of the first "basic" APD machine according to the present invention.

Figure 2 schematically illustrates one of the liquid input/output ports and a portion of the occluding mechanism in the machine at Figure 1.

Figure 3 shows an exploded view of the occlusion mechanism for an automated peritoneal dialysis machine according to the present invention.

Figure 4 is a graphical representation of the variation of intraperitoneal pressure versus time during the cycles of an apparatus according to the present invention.

Figure 5 is a graphical representation of the volume of fluid removed to stabilize pressure as a function of time during the DWELL period of a dialysis cycle, as measured using APD apparatus according to the present invention.

Figure 6 is a schematic illustration of a second embodiment of APD machine according to the present invention.

Figure 7 is a schematic illustration of a second embodiment of APD machine according to the present invention.

Figure 8 is a preferred version of the apparatus embodiment of Figure 7, in which components are structurally integrated into a compact cartridge.

Figure 9 is a schematic illustration of a fourth embodiment of apparatus according to the present lnvent lon .

Detailed Description of the Invention A "basic" layout of components of apparatus according to the present invention is illustrated schematically in Figure 1. The apparatus is connected to the peritoneal cavity of patient 10 by means of a patient tubing line 12, through which fresh fluid is infused and spent fluid is withdrawn.

An essential component of apparatus according to the present invention is an occlusion manifold 14, the hollow interior communication channel 16 of which is in communication with all of the fluid input lines to containers of selected dialysate solution components and to output tubing lines to the catheter and to drain.

In the arrangement shown in Figure 1, eight separate input or output connection ports into channel 16 of cartridge 14 are shown, numbered 1 to 8. Containers (solution bags) S1, S2 carry sterile PD solutions of two different electrolyte compositions and are connected to cartridge inputs 1 and 2 by tubing lines L1 and L2, respectively. In-line heaters 13 are provided, as is conventional in PD apparatus, to warm the sterile PD
solutions to body temperature. Containers S1 and S2 could alternatively carry standard PD solutions (glucose or similar as the osmotic agent).

Input 3 of manifold 14 is connected by line L~ to a container G1 of highly concentrated sterile osmotic agent (glucose solution or other known osmotic agent).
Container bags M1 and M2 connected by lines L4 and L5, respectively, to the corresponding manifold inputs could contain different medications or additives to improve the clinical value of the solutions in S1 and S2. Apparatus according to the present invention includes a precise metering pump P1 whose operation is described in more detail below. Aforementioned patient line 12 is connected to input 7, while a drain line 15 is connected to port 8.

For registering and monitoring the interperitoneal pressure from time to time during the course of treatment, a pressure transducer means 17 is preferably included, the signal from which is monitored by electronic control means for the apparatus (not shown).

A preferred arrangement for the occlusion mechanism of occlusion manifold 14 is illustrated in Figures 2 and 8. Figure 2 schematically illustrates one of the tubing connecting ports 18 onto which an input tubing line L
fits. Port 18 communicates with interior communication channel 16 of occlusion manifold 14.

To ports 18 there correspond flexible sealing diaphragms 20, each positioned in the wall of manifold 14 opposite the wall through which corresponding port 18 enters channel 16, and electronically controlled plungers 22.

-CA 022ll848 l998-07-27 Figure 3 shows an exploded view an assembly of plungers 22 and 22c, springs 22a and 22b and motors 23 for assembly of an occlusion mechanism of the manifold of automated PD apparatus according to the present invention. In assembly, plungers 22 and plunger springs 22b are first inserted into manifold 14c. Cams 23a attached to individual small rotary motors 23 are inserted into the manifold, so that the plungers are retained inside the manifold by the cams and ride directly on the cams. The small springs 22a and corresponding plunger heads 22c are inserted from the top into respective plungers 22 through the manifold. All the motors 23 are mounted on a motor mounting plate 24.
Two screws 24a are used to secure motor mounting plate 24 to manifold 14c.

Each motor 23 rotates its associated cam 23a and corresponding plunger 22c follows the cam for up or down movement. The respective up and down positions of the individual plungers 22 can be sensed electronically and a signal sent to the microprocessor means for stopping motors at up or down plunger positions as appropriate.
The tubing connecting ports 18 terminating inside channel 16 of manifold 14 align with plungers 22c. The "up"
position of a plunger has the effect of occluding the cartridge port to which it corresponds, while the "down"
position opens the port. Fluid flows may accordingly be controlled as discussed below.

It is contemplated that the machine will be controlled by microprocessor means (not shown), having stored memory for on-line monitoring of information and for programming of set operational parameters. A
removable memory card can also be incorporated to ensure easy collection and transfer of treatment data for the patients. Optionally, an interactive voice interface and visual and audio alarm systems can be incorporated to - - - - - - - - -simplify the diagnosis of problems during and after PD
treatments.

The microprocessor means is programmed for receiving signals from various sensors and for producing output control signals for controlling the metering pump P1 and plungers 22 through an electromechanical means such as the motor/cam arrangement discussed above.

During dialysis, the desired filling fluid volumes of each cycle are programmed into the microprocessor.
The ratios of the corresponding medications and/or additives are also entered. Initializing the machine operation, all input and output ports of the cartridge 14 are closed by their respective plungers. These plungers are controlled individually by their respective motors.
When plunger 22c moves upwards (i.e., toward the manifold), it pushes against flexible diaphragm 20, closing the outlet of port tube 18 within channel 16 of the manifold, precluding entry or withdrawal of fluid from the chamber by way of that port. Moving the plunger downward leaves the tube outlet in communication with the chamber, so that fluid may flow freely in or out of the chamber and communicate with any other outlets which are also open at that time.

Referring specifically to Figure 1, the microprocessor electronic control means is programmed so that port #8 (to drain line 15) and port #6 (to the metering pump pumpline) are opened. In sequence, the plungers corresponding to input/output ports numbers 1, 2, 3, 4 and 5 are activated thus opening and closing input ports 1,2,3,4 and 5 at predetermined times. During the opening period, metering pump P1 operates to draw fluid in from respective container bags and to flush them out to the drain. Patient line 12 is flushed by opening either #1 or #2, opening #6 and drawing fluid out of -either S1 or S2, then closing #1 or #2, opening #7 and infusing the fluid into patient line 12.

For efficient operation in drawing calibrated volumes of fluid from container bags and infusing the withdrawn fluid to target locations, whether the container bags and the target locations are vertically above or below the machine, it is essential that metering pump P1 provide positive displacement of fluid and have a known volumetric displacement. One way this has been arranged in practice has been to have a variable volumetric displacement mechanism included in the metering pump P1. Variable displacement was achieved with controlled linear translation of a volume displacement member. This type of motion was achieved by coupling a worm gear to the output driveshaft of an electric motor. The controlled rotary motion of the electric motor is then smoothly translated into a controlled linear motion which in turn will adjust the volumetric displacement of the pump.

A common example of this type of metering pump is a syringe pump with controlled linear translation of the plunger in the barrel of the syringe. The linear motion (volume displacement) of a metering syringe pump was calibrated in the following manner. The internal shaft on the electric motor was digitally encoded. Its rotary position was optically sensed thus generating a set of electrical pulses whose number were directly proportional to linear displacement of the worm gear. One particular configuration which was used in this way gave a fluid displacement of 20cc for each 2.15 inches of linear travel of the worm gear. The lead screw of the worm gear had a lead of 0.12 inches and was driven through a gear box (gear ratio 81:1). The encoder of the motor produced 512 pulses/revolution. The microprocessor control means, through linkage to the motor shaft encoder, could track each pulse generated by the encoder. In principle this metering system had a sensitivity of 30 x 10-9 litres.
This is at least 3 orders of magnitude more precise than required for APD apparatus according to the invention to achieve its metering objectives. Naturally those skilled in the art could construct a number of variations of this particular device.

During FILL mode if solution S1, say, is selected, ports numbers 1 and 6 would be opened and the metering pump activated to draw the correct amount of fluid from container bag S1. That done, port #1 closes and desired additives G1 selected by opening port #3, drawing the correct volume into P1, then closing port #3. Continuing in this way, incremental additions can be made of fluids from M1 and M2 into the pump. Then, to infuse the metered fluid composition into the patient, port #7 opens and the metering pump causes the fluid to be injected into the peritoneal cavity of the patient, while the machine monitors the volume of fluid instilled into the patient.

This injection procedure is repeated several times until the correct total amount of dialysis fluid has been delivered or some other predetermined state is achieved.
A graphical example of such a predetermined state is shown in Fig 4 at point P2. During the FILL mode, the intraperitoneal pressure will increase slowly from To to T1 and in proportion to the filled volume. There is an inflective increase in pressure at the maximum fill volume attained at time beyond T1 and corresponding pressure P2. The machine will be programmed to remove enough fluid to back off the pressure from the maximum P2 to a safe and controlled pressure level P1. This would be the steady state pressure for the monitoring process.
The official DwELL period then begins at T2.

Turning to the DwELL period, all ports of the manifold are closed and variations in the interperitoneal pressure are monitored by the microprocessor from signals CA 022ll848 l998-07-27 transmitted by in-line pressure transducer 17. Any ultrafiltration which occurs (drawing fluid from the body of the patient into the peritoneal cavity) will necessarily result in an increase in intraperitoneal pressure which, on detection, signals the control means to open ports #s 6 and 7. Pump P1 will then suck back sufficient fluid, namely, the-excess amount, from the patient's peritoneal cavity until the steady state pressure level (P1) has been restored. The volume which has been so removed during the DWELL period is recorded by the computer as "ultrafiltration" with respect to the time it was taken. Whenever the pressure reaches P2, the pump is activated to reduce the fluid volume enough to drop the pressure back to the steady state P1. This volume Vf iS recorded with respect to time t2 (the length will be dependent on osmotic pressure of the fluid). This action is operated as often as it may be necessary.

This process of restoring steady state pressure and recording the cumulative volume of fluid removed as a function of time in order to do so, is carried out automatically throughout the DWELL period and the measure of cumulative ultrafiltration (UF) is recorded. A
graphical measurement of intraperitoneal pressure versus time affords valuable diagnostic information. When the pressure does not change from its steady state value for a predetermined period of time, it may be inferred that the dialysis fluid is no longer performing its optimal clinical function. At such a time, T3 (Fig 4), the fluid can be safely drained out of the patient without waste of further time. An onset of a pressure drop, however, would indicate that the patient is absorbing fluid from the peritoneal cavity which could indicate that the patient is absorbing glucose from the dialysate, or that dialysate is leaking into extra-abdominal tissues. These undesirable clinical conditions are avoided by arranging the control logic of the machine to automatically drain out all spent dialysate volume from the patient when such pressure drop occurs.

During the DRAIN mode ports #6 and #7 are opened. The metering pump P1 draws the spent fluid from the patient and into the syringe. This volume is measured as it is being withdrawn. When the syringe is full, port #7 closes and port #8 opens. The pump P1 reverses its direction and pushes the waste fluid from the syringe through the drain line and into a receptacle for spent dialysate. This is operated until all the fluid is drained out or the pressure registers negative, or until the end of the set DRAIN time. The final UF is then determined by the machine.

This completes one dialysis cycle. The above procedure is repeated as many times as required until the desired amount of treatment is obtained.

Another important characteristic of this invention is its ability to make decisions based on real-time physiological needs of a patient or provide previously unattainable clinical information. A graphical representation of the on-line monitoring of volume of fluid removed in order to stabilize pressure at a steady state, as a function of time during the DWELL period of one dialysis cycle, is provided in Figure 5 and is but one such example of new clinical information. The invention will allow the normal set DWELL time (T2 to T3 ) to be rationally adjusted. At maximum UF volume, Vml the dialysis fluid has reached equilibrium with the plasma in the peritoneal membrane. Therefore anytime beyond Tx, would be treatment time wasted. A clinician could either program the machine to automatically drain the patient of the spent fluid and introduce fresh fluid for better dialysis or use the information to set more effective DWELL time for the next treatment. Alternatively if the set DWELL time terminates at the rising phase of the CA 022ll848 l998-07-27 ultrafiltration curve, then the dialysate is not being utilized properly. These are examples of the ability of the apparatus to automatically make decisions based on real-time physiological needs of a patient. This graph also reflects real time solute and fluid transport rates of the peritoneal membrane for any given dialysate formulation. That is, the greater the efficiency of the peritoneal membrane the greater the initial slope of the ultrafiltration curve and or the faster time Tx is achieved. For the first time clinicians will be able to quantify the transport characteristics of the membrane on-line and use this information to directly control the machine or allow the machine to make the necessary adjustments automatically.

A further example of the capability of apparatus according to the invention in providing previously unattainable clinical information and/or intelligent use of such information by the APD machine is as follows: In clinical PD applications, the characteristics of the peritoneal membrane with respect to its active surface area, and permeability (solute and fluid transport) are all variable and mostly unknown for any given patient.
Hence methods have been developed to quantify peritoneal membrane performance. However, these methods are complex, indirect and none of them are on-line analytical procedures. Two methods used for assessing membrane performance are (a) the peritoneal Membrane Mass Transfer Area Coefficient (MTAC) and (b) the Peritoneal Equilibration Test (PET). . The later (PET), determines the ratio of dialysate-to-plasma (D/P) of a given solute and is the one most commonly used to assess patients. At best this is performed once a month. Currently it is impossible to obtain data to perform PET at various stages of the DWELL period during treatment. If this time dependent data could be obtained it could lead to a better clinical understanding of the different types of ultrafiltration failures. Combining the unique ability -of apparatus according to the present invention to secure a sample of the fluid during DWELL at known correlated points on the ultrafiltration curve clinicians will be better able to properly evaluate the PD treatment in vivo. This represents a major advance in the art of PD
treatment. A related clinical advantage is that clinicians will immediately be able to correlate changes in ultrafiltration curve with the type of medication or additive used during a treatment cycle.

It will be appreciated from the foregoing that the pressure monitoring activities used to control the UF
using a machine according to the present invention makes it possible to perform a true tidal peritoneal dialysis.
By maintaining the pressure at its initial fill pressure P1 we can infer that the actual volume of fluid in the cavity is the same as the initial fill volume. This volume is known. For the first time an APD machine will be able to use the actual volume of fluid in the peritoneal cavity and not a pre-estimated amount to determine the actual tidal withdrawal and refill volumes.
This is a major improvement in the art.

Moreover, additional detectors and sensors may be included in the system and their signals taken into account to a programme microprocessor or diagnostic and therapeutic advantage. For example, a turbidimeter including a light source and light detector monitoring the clarity of the effluent during DRAIN can give early detection of the onset of infection. If patient line 12 is passed between such a light source and light detector, it will be possible to detect whether or not the patient's effluent is cloudy during DRAIN, owing to an onset of peritonitis (production of enhanced level of light-scattering white blood cells brought about by infection). The detector will transmit this information to the microprocessor and audio and visual alarms may be initiated, the machine triggered to empty metering pump CA 022ll848 l998-07-27 P1 and a sample of cloudy effluent collected for further analysis.

The machine could therefore be programmed to make important decisions as to the infusion pattern on the basis of signals from sensors reflecting the composition and pressure of fluid in the peritoneal cavity.

Alternative Embodiments of Apparatus Although the "basic" machine shown in Figure 1 employs a metering pump to draw and deliver the apportioned dialysate components, the arrangement could be used without a metering pump at all, but employing a weighing system and gravity for the discharge of sterile fluids and medications from container bags supported vertically above the patient, with a weigh bag located below the patient for determining the volume.

Equally as valid, although the basic machine is designed to customize the dialysate from a plurality of solution bags, the machine can be used in a non customisation mode, i.e., with dialysate pre-mixed in each of one or more container bags. Each port can be connected to a dialysate of fixed formulation. The described diagnostic power of the apparatus can then be used to select which port is connected to the patient line (12) to FILL the patient, determine the DWELL period, and drain the patient of that selected formulation using the metering pump.

A second embodiment of a PD apparatus according to the present invention is illustrated schematically in Figure 6. The same reference numerals are used in Figure 6 and in the below-discussed Figures 7 and 8 to identify parts of the apparatus which are entirely analogous and co-functional with like-numbered components of the basic machine shown in Figure 1.

The second preferred embodiment as shown in Fig 6.
depends on pump P1 for achieving compact arrangement and ease of clinical use and uniqueness in portability. The cartridge is divided into two distinct chambers 14a and 14b. The first chamber houses ports #1, #2, #3, #4, and #5. The second chamber houses ports #6, #7, and #8. The ports #4 and #7 are now connected to the metering pump P1 via one way valves V1 and V2 for fluid inflow and outflow respectively. The bulk sterile neutral fluid S (no osmotic agent), is connected to port #1 through heater 13. The osmotic agent G1 (i.e. glucose etc.) is at port #2, and the medication M1 is at #3. The inflow to the patient is at port #6 and the outflow from the patient is at port #5. Port #5 and #6 are joined to the patient line via the pressure transducer means 17.

In operation all the ports are initially closed.
During FILL mode #1, #4, #6, and #7 are opened. The fresh fluid is drawn in by P1 from S through the heater, through the valve V1. At a predetermined volume #1 closes, #2 opens and the correct amount of the osmotic fluid is also drawn into the metering pump. The port #2 then closes and #3 opens to allow the withdrawal of the desired volume of the medication M1 into P1. Then #3 is closed. Reversing direction the contents of P1 is discharged into the patient via V2, pressure transducer 17 and the patient line 12. The above procedure is repeated several times until the correct dosage volume is delivered to the patient. By having unidirectional valves V1 and V2, the frequency of closing and opening of ports #4, #5, #6, and #7 is reduced.

During DRAIN mode only plungers #4, #5, #7, and #8 are opened. The spent fluid from the patient is drawn into P1 through the patient line, the pressure transducer 17, through #5, #4 and Valve V1. The syringe P1 measures the drawn in fluid accordingly. The feedback of the -- -- -- ---- --CA 022ll848 l998-07-27 pressure transducer regulates the rate of fluid drawn in by P1 from the patient. When full, P1 is emptied through V2, plungers #7 and #8 to the final drain. All the previously mentioned activities are equally applicable to this version. Plungers #4 and #7 are not strictly necessary, because, with plungers #s 1, 2, 3, 5, 6 and 8 all closed, the metering pump is isolated and there is no movement of fluid.

A machine according to this second embodiment could be operated from a normal table top or a short stand, with the solutions and medications located conveniently below the main machine. The machine could even be operated at the floor level. The positive displacement pump P1 ensures that the efficiency of the delivery system does not depend upon the relative vertical positions of the solutions, the patients and/or the final drain, as is the case in gravity-fed cyclers. This therefore makes the new machine universal for patients on normal beds, hospital beds or lying on floor mats.

A third preferred version is as shown in Figure 7.
The component arrangements are similar to the first version shown in Figure 1 (the Basic Machine), discussed above. The sterile PD solution (electrolytes only) is at port #1. The Osmotic agents (G1, G2) are at ports #2 and #3. The medication M1, is at port #4. The Patient line 12 is controlled by port #5. And port #6 controls the drain line 15. The metering pump P1 communicates directly with the whole occlusion chamber. And the fluid flowing in and out of metering pump P1 passes through a pressure transducer chamber 17' that communicates with pressure transducer 17. All the tubing lines communicate with occlusion manifold 14. Pressure in the lines, and hence in connected bags, or in the patient and in the drain line are all monitored by opening the appropriate port.
Using this arrangement, the pressure readings could be used to detect other important conditions in addition to -all those already discussed under the previous versions;
the detection of these, (a) empty solution bags (S, G1, G2 & M1) (b) obstructions in the drain line and (c) obstructions in the patient line.

A "compact cartridge" version of the system of Figure 7 is as shown in Figure 8. The occlusion block 14, the heater and metering pump P1 are all integrated into a single compact cartridge. The heating chamber is divided into two sections: the initial heater chamber 13a that houses the incoming cold solution, and the corrugated heater section 13b that directs the fluid path to ensure proper heating of the solution. The output of the heater is attached to port #1.

A preferred embodiment of the new APD apparatus is as shown in Figure 9. The operation of this embodiment is the same as the one discussed above for the third version in Figure 7, except in this embodiment there are two additions, namely (a) effluent detector 28 and (b) sample collector port (at #6). The drain line 15 is now located at port #7.

The effluent detector comprises of a light source 28a facing a light detector 28b. Variations in the light intensities are detected by the light detector and the signals transmitted to microprocessor for the appropriate actions.

The patient line 12 passes between the light source 28a and the light detector 28b of the effluent detector 28. Hence during DR~IN if the patient's effluent is cloudy (due to an onset of peritonitis; infection-production of white blood cells), the light beam to thelight detector is diffused. The detector transmits the message accordingly to the microprocessor. Both audio and visual alarms are initiated. When this happens the machine automatically, at the point of emptying the metering pump P1, opens port #6 and sends a sample of the cloudy effluent solution into the sample collector container 30 (which couid be a bag or a syringe). Then port #6 will be closed and the normal drain procedure will be continued by operating port #7.

If the apparatus had been set up to initiate peritonitis treatment, rapid peritoneum flush or flushes (fills immediately followed by drains), will be carried out. Then followed by treatment fill volumes containing medication or medications, automatically metered from the medication containers such as M1, by the metering pump P1.

The effluent detector, similarly, will detect excessive amount of blood in the effluent (usually with new catheter operations or with new catheter break-ins), and could be programmed to automatically reduce the amount of heparin additive and or reduce the dialysate infusion volumes.

While particular embodiments of this invention have been described in relation to the accompanying drawings, it will be evident to those skilled in the art that changes and modifications may be made therein, without departure from the spirit of the invention as defined in the appended claims.

Claims (7)

1. Apparatus for carrying out peritoneal dialysis on a patient whose peritoneal cavity is in communication with at least one patient catheter, said apparatus comprising:
(a) a manifold comprising a plurality of liquid input/output ports;
(b) occlusion means for selectively sealing off and re-opening communication between any one or more of said input/output ports and the other ports of the manifold;
(c) metering means in communication with at least a first one of said input/output ports, operable to withdraw and measure the volume of selected quantities of liquid from said manifold;
(d) a mixing chamber in communication with the manifold;
(e) a patient conduit line for connecting at least a second one of said input/output ports to said patient catheter;
(f) conduit lines for connecting others of said input/output ports to respective container bags of dialysate solution components; and (g) means for controlling said occlusion means and said metering means, whereby a selected volume of each of selected ones of said dialysate components is withdrawn by said metering means to provide a dialysis solution in said mixing chamber of a desired final formulation.

2. Apparatus according to claim 1, wherein said means for controlling said occlusion means and said metering means consists of electronic control and sequencing means, operable to cause a selected volume of said final formulation dialysis solution to be injected through said patient conduit line into the peritoneal cavity line of the patient in a FILL phase and, after a first selected time in a DWELL phase, to be withdrawn from the peritoneal cavity into said metering means.

3. Apparatus according to claim 1 or claim 2, further comprising a drain conduit line for connecting a third one of said input/output ports to a receptacle for spent dialysate, said electronic control and sequencing means being operable in a DRAIN phase following said first selected time to cause all or part of the spent dialysis solution withdrawn into said metering means to be injected through said drain conduit line into said receptacle.

4. Apparatus according to any one of claims 1 to 3, wherein said metering means comprises fluid transfer means including a pumping mechanism and reservoir means of calibrated variable volume, and electromechanical drive means operable to vary the volume of said reservoir means in a program of stepped increases or decreases of said calibrated volume in response to control signals from said electronic control and sequencing means.

5. Apparatus according to claim 4, wherein said metering means comprises a syringe pump having a syringe plunger and electromechanical drive means for stepped advancement or retraction of said syringe plunger in response to control signals from said electronic control and sequencing means.

6. Apparatus according to any one of claims 3 to 5, further comprising means for monitoring the intraperitoneal pressure of the patient and producing a first monitoring signal to said electronic control and sequencing means for use in determining and implementing operation steps of the apparatus appropriate to desired therapeutic treatment of the patient.

7. Apparatus according to any one of claims 3 to 6, further comprising electro-optical means for producing a second monitoring signal to said electronic control and sequencing means, said second monitoring signal being indicative of the turbidity of fluid in said patient conduit line at a selected time, for use in determining and implementing operations of the apparatus appropriate to desired therapeutic treatment of the patient.