the implantable cranium pump unit 100 of the illustrated embodiment of the invention depicted in fig1 a comprises of two distinct polymer layers ; an inner membrane 107 and the outer membrane 106 as best seen in fig1 c . inner membrane 107 and outer membrane 106 are seamed together at the base and head of cranium pump 100 by a pump solenoid assembly 104 and a pump head assembly 103 respectively ( fig1 ). the pump solenoid assembly 104 and pump head assembly 103 provide a means for contracting and expanding the cranium pump 100 and are further discussed in more detail below . both inner membrane 107 and outer membrane 106 are made from a skin - like polymer material . this material allows the pump 100 to be highly flexible during the drug delivery process and decreases the chances for infection or rejection from the body of a patient . the space enclosed by inner membrane 107 is a medication reservoir 129 used for storing a medicating agent or a mixture of medicating agents as shown in fig1 . the size and volume of the medication reservoir 129 and thus the cranium pump 100 itself may be varied from patient to patient . a physician will make a determination of how much medication a particular patient will need and then the size of the medication reservoir 129 will be made accordingly . for example , a patient that needs large doses of medication will receive a cranium pump 100 with a larger medication reservoir 129 then a patient who only requires a small dose . turning again to fig1 a - 13 c , the inner membrane 107 further comprises a plurality of small injector spines 108 distributed throughout the entire surface of the inner membrane 107 . as can be seen in fig1 a and 14 b , the injector spines 108 may be comprised of hollow tubes 109 or a spiral design 133 with a pleated inlet 110 at its base where spine 108 meets the inner membrane 107 ( fig1 c ). the inner membrane 107 has a shape memory which effectively causes it to act as telescoping springs to rapidly extend and retract the injector spines 108 through the surface of the outer membrane 106 . the injector spines 108 are also sufficiently long enough to penetrate the outer membrane 106 when the cranium pump 100 is in its most expanded state as shown in fig1 a . the injector spines 108 are tapered at their tips so that fluid flows substantially in only one direction , namely from the medication reservoir 129 to the surrounding tissue of the patient . when the cranium pump 100 is being contracted or is in its supply stroke , the inner membrane 107 is pushed outward thus extending the injector spines 108 further past the outer membrane 106 and deeper into the patient &# 39 ; s surrounding tissue . this process allows the pump 100 to deliver medicating agents deeper into the affected tissue and thus the tumor itself in a more direct way than any prior art method . the injector spines 108 extend into the patient &# 39 ; s tissue and the increased pressure created by the contracting cranium pump 100 pushes the medicating agent out through the injector spines 108 at its most extreme extension point . when the cranium pump 100 is expanding or is in its intake stroke , the inner membrane 107 collapses back to its original shape and thus retracts the injector spines 108 to their original position just outside of the outer membrane 106 . when the injector spines 108 are retracted , the pressure differential of the cranium pump 100 will necessarily draw in a small amount of surrounding cerebral fluid into a sampling cavity 111 . this is deemed beneficial however since the cerebral fluid will be eventually mixed with the medicating agent and thus increasing the diffusion rate of the medicating agent when it is pushed out of the injector spines 108 in any of the subsequent supply strokes . this process of extending and retracting the injector spines 108 is repeated for as long as the cranium pump 100 is activated . returning to fig1 c , the outer membrane 106 further comprises a plurality of micro pores 112 distributed throughout its entire surface . when the pump 100 is in the intake stroke , cerebral fluid is drawn into the pump 100 through the micro pores 112 due to the pressure differential that exists between the inside of pump 100 and the surrounding area outside of the pump 100 . the amount of cerebral fluid that is drawn through the micro pores 112 is kept separated from the medication reservoir 129 by the inner membrane 107 and the lower portions of the injection spines 108 . the volume of cerebral fluid that is then contained between the inner membrane 107 and outer membrane 106 then forms a sampling cavity 111 . the components of cranium pump 100 is preferably composed of silicone , as this is the material currently used for ventriculoperitoneal shunts . however additional materials such as biodegradable material or other composites may be used without departing from the original spirit and scope of the invention . the detailed parts of the pump head 103 and pump solenoid 104 assemblies are shown in fig1 a - 16 b . in fig1 a , the assembly is comprised of a coil 119 which can generate magnetic fields either reinforcing or opposing the magnetic field of a permanent magnet 118 . the permanent magnet 118 is made of nbfe35 ceramic material however other materials may be used without departing from the original scope and spirit of the invention . the coil 119 may then be pulled or pushed away from the permanent magnet 118 depending on the current polarity of the coil 119 . the coil 119 is coupled to a bobbin 120 and is constructed from a plurality of small ( 40awg ) windings . the bobbin 120 is composed of several layers of bobbin washers 121 because bobbin 120 is attached to the flexile skin - like material of the inner membrane 107 , the coil 119 movement translates into an increase or decrease of pressure on the medication reservoir 129 . controlling the amount of electrical current that passes through the coil 119 produces variable and regulated medication pressure which in turn adjusts the amount of medicating agent passing through a plurality of injector spines 108 described above . conversely , the controlled movement of the coil 119 acts as a pumping function serving to provide suction to the outer membrane 106 of the pump and thus draw in surrounding cerebral fluid from the patient . the apparatus uses a method similar to respiration to not only pump drugs into the brain , but also to sample the immediate area by creating a negative pressure in the sampling cavity 111 . as can be seen in fig1 , the pump solenoid 104 and pump head 103 use a magnet 118 and coil 119 as a solenoid to create attraction or repulsion between the pump head 103 and the bobbin 120 . this motion is then translated to the cranium pump 100 . the outer membrane 106 is made of a more ridged durra silicon rubber than the inner membrane 107 . when the pressure is reversed by the pump solenoid 104 , because the inner membrane 107 is softer than the outer membrane 106 , the gap between the membranes increases and the negative pressure sucks in the cerebral fluids through the aspirator micro - pores 112 around the spines 108 on the outer membrane 106 . turning back to fig1 a and 15 b , this sample fluid then gets removed between a sampling washer 115 through sampling collection ducts 128 in a delivery / sampling head 114 and out through a connector plate 113 . the connector plate 113 has both a drug inlet 122 and a sampling tube 123 connection . the connector plate 113 also comprises all the electrical connections for the coil 119 , the pressure sensor 131 ( shown in fig1 ) and the temperature sensors 132 ( also shown in fig1 ). the top of drug inlet 122 and the sampling tube 123 as we , l as various sensor and coil connections can be seen in fig1 b . fig1 a and 16 b best show that the electrical connections are transferred through a series of sensor and coil pins 126 through the delivery / sampling head 114 to a plurality of sensor and coil connections 125 in the inner medication reservoir 129 . connections to the coil 119 are made with insulated flexible wire 130 ( shown in fig1 ). turning back to fig1 a and 16 b , the inner and outer membranes 107 , 106 are attached and compressed by washers 121 to the bobbin 120 . the bobbin 120 freely travels over the permanent ndfeb magnet 118 . the magnet 118 is permanently coupled to the delivery / sampling head 114 . the inner and outer membranes 107 , 106 are also coupled directly to the delivery / sampling head 114 . the sampling washer 115 and the bobbin 120 also provide the necessary gap of 0 . 020 inch for the medication reservoir 129 . a compression nut 117 compresses an inner membrane washer 116 to clamp the inner membrane 107 against the delivery / sampling head 114 . as seen in fig1 b , the delivery / sampling head 114 also comprises a drug dispersion tube 124 which releases the medicating agent or mixture of medicating agents to be administered to the patient into the medication reservoir 129 . turning back to fig1 a , at the head of the cranium pump 100 , the pump head assembly 103 located there is coupled to a seal connector 102 via a series of fluid lines and electronic connections enclosed in a pump - to - seal interconnect 101 . the seal connector 102 is essentially a valve that controls the amount of fluid that is permitted to enter or leave the pump 100 . when more medicating agent is needed , the seal connector 102 opens and allows the medicating agent to travel through the pump - to - seal interconnect 101 and enter the medication reservoir 129 below . when the correct amount of medicating agent has been applied , the seal connector 102 closes and all incoming fluid flow stops . additionally , the seal connector 102 houses a suction nozzle ( not shown ) that applies suction to the sampling cavity 111 and draws up recently acquired cerebral fluid up and out of the pump 100 and through the seal connector 102 . [ the reference numbers and discussion in fig1 b and 10c are not correlated to or even seem to relate to the prior discussion of the elements and operation of fig1 a , 11 a - 16 b !!!!! delete paragraphs 106 - 108 ?] fig1 b and 10 c further depict the pump mode 145 and supply mode 144 as it is employed by the cranium pump 100 . fig1 b and 10 c depict the electrostatic muscle 64 in its closed state 134 which is also the supply mode 144 , where the medicating agent or brm are pumped out and transported from the cranium pump 100 to the desired tumor site or biological tissue of interest . in fig1 b , the inlet nozzle is shown as 136 , while an increasing chamber volume 141 is taking place . the increase in chamber volume causes flow 138 from the inlet 136 to enter the chamber 142 and at the same time , there is a small amount of fluid which flows from the outlet 137 into the chamber 142 as well . however , because of the venturi action of the inlet 136 and the outlet 137 , the total net flow is from the cranium pump 100 into the chamber 142 . in this case , the inlet 136 exhibits a diffuser action 143 and the outlet 137 exhibits a nozzle action 140 . fig1 c exhibits the electrostatic muscle 64 in its open state 135 , which is also the pump mode 145 . in this case there is a decrease in chamber volume 151 , which causes a net flow to take place from the chamber 150 to the tumor site 41 through the outlet 148 . although there is a small amount of flow 147 , from the chamber 150 to the inlet , the net flow is substantial and is from the chamber 150 to the tumor site 41 . in this mode , the inlet 147 exhibits a nozzle action , 152 and the outlet exhibits a diffuser action 149 . turning to fig1 a , a delivery hose 200 is coupled to the seal connector 102 and a cpd 1 portion of the apparatus . the delivery hose 200 thus serves as a conduit between the pumping and analyzing portions of the current invention and houses a refill line , a return sample fluid line , and several electronics connections for various sensors and the coil 119 . after the cranium of the patient has been opened and the skull and dura have been successfully breeched , the tumor , or as much of the tumor as possible , is removed . the soft cranium pump 100 is then placed in the resulting cavity , and the skull cap is reattached . as can be clearly seen , the pump 100 is positioned on the patient &# 39 ; s brain beneath both the dura and skull of the patient . the seal connector 102 is coupled to pump 100 and is firmly embedded within the dura of the patient with the top portion of the shunt protruding from the skull . the delivery hose 200 is coupled to the seal connector 102 and leads away from the pump 100 and down the back of the neck of the patient underneath the skin . the delivery hose 200 lies beneath the scalp of the patient for the entire distance between the seal connector 102 and the point where the catheter is connected to the analyzer 1 at the clavicular head . the purpose for maintaining the catheter 200 beneath the scalp is to give the patient a sense of normalcy and confidence while they are undergoing treatment . fig1 b shows an external data 300 logger which communicates with the chemotherapy pump device ( cpd ) 1 . the cpd 1 communicates with the external controller 300 by the use of rf transmitter 304 and its associated antenna 32 and rf receiver 303 with its associated antenna 301 . after implantation of the cpd 1 subcutaneously inside the patient 39 , the system allows for programmability of the device in order to dispense the medicating agent in proper intervals over time and in the prescribed doses . once the cpd 1 and cranium pump 100 is implanted and is in operation , the clinician may decide to change the parameters of the operation such as the amount of medication dispensed onto the tumor site or the time intervals associated with the dispense process . the clinician communicates with the internal electronics of cpd 1 using an external programming device 300 shown in fig1 b , which may be in the form of a desktop computer or any other similar appropriate device . the device 300 is able to communicate with the microcontroller in cpd 1 through its own microcontroller 305 via rf transmitter 304 , its antenna 302 , and the rf receiver 303 and its antenna 301 , or via the serial communication port 307 , located in the external control box 300 . the new sets of commands are then transferred to the cranium pump 100 . these new command data are then stored in the memory of the microcontroller of cpd 1 , which is now programmed anew to perform the procedure as coded in the new instruction set . the microcontroller located in cpd 1 and implanted inside the patient &# 39 ; s body 39 communicates with the external control 300 via rf transmitter 304 and rf receiver 303 thereby sending its collected data to the external data logger 300 . this feature enables the clinician to collect data and to determine the state of the patient throughout the period of treatment . these data are stored inside the external controller 300 providing chart history of the treatment status of the parameters associated with the tumor site . the cpd 1 transmits data for collection and storage . the data logger 300 is controlled by the user via the settings in control 308 and it also displays the amount of medicating agent dispensed over time by the cranium pump 100 on its display 309 . data collected in this manner can be used to correlate behavior pattern of a particular patient and his or her chart history . one can write a data collection and analysis program which can be displayed by the controller 300 . once the data are collected from the cpd 1 , the external controller 300 or the host pc can then plot the data on a time scale and analyze the data further . it is significantly better to correlate between the input and the output or between cause and effect to mirror the action of the cranium pump 100 and its host tumor site . such data in the form of historical plot of cause and effect benefit the patient 39 and aide in future research . the entire unit as shown in the figure is run by power obtained from its power source 306 . fig1 c is an illustration of a patient 39 with tumor of the form glioma with the implanted pump 100 . the controller 300 with its associated serial port 307 and receiver and transmitter antennae 303 and 304 respectively is shown in its bidirectional communication model with the implanted cpd 1 via the rf path 310 . turning to fig4 a , the cpd 1 comprises a delivery connector 7 where the delivery hose 200 couples with the cpd 1 . the delivery connector 7 contains a drug outlet 4 , a sample return 5 , and a plurality of sensor connections 6 for controlling the pump unit 100 and for analyzing the sample fluid that is obtained from the cranium of the patient . the drug outlet 4 is the aperture in which medicating agents are sent from the cpd 1 through the delivery hose 200 . similarly , the sample return 5 is the aperture where cerebral fluid that has been collected by pump 100 is returned by the delivery hose 200 and enters the cpd 1 for analysis . the process by which the external cpd 1 sends medicating agents and receives sample fluid obtained from the patient through the delivery hose 200 is explained in further detail below . up to four drug ampoules 2 ( fig2 ) can be deposed on the bottom portion 10 of the external cpd 1 in four separate ampoule bays 8 as depicted in fig3 d . it is to be expressly understood that fewer or additional ampoule bays may be present without departing from the original spirit and scope of the invention . to introduce a medicating agent into the cpd 1 , a drug ampoule 2 is inserted into the ampoule bay 8 . drug needles 18 extending from the interior of the cpd 1 shown in fig7 a penetrate the ampoules 2 and carry the medicating agent . the cpd 1 then draws in the medicating agent in a series of steps that are described below . turning to fig6 , the interior of the cpd 1 is comprised of two assemblies ; a pump electronics assembly 12 and an induction charger assembly 11 . the pump electronics assembly 12 and the induction charger assembly 11 are both housed within the external cpd 1 and are joined by an electronics interconnect cable 13 as best seen in fig7 a and 7 b . the pump electronics assembly 12 is shown in greater detail in fig8 a and 8 b . as seen in fig8 b , the pump electronics assembly 12 contains a drug deliver cpu 27 that stores its program and data into two flash memories 28 . pre - stored information such as look - up tables and the like are stored on the flash memories 28 . the drug delivery cpu 27 runs a pre - installed intelligent chemo delivery software program and controls an ampoule pump integrated circuit 20 , a return pump integrated circuit 19 , and a delivery valve drift integrated circuit 22 as seen in fig8 a . the drug delivery cpu 27 also communicates with a lab - on - a - chip 21 and receives important treatment data such as sample temperature data through the sensor inputs 6 in the delivery connector 7 seen best in fig6 . the drug delivery cpu 27 is pre - programmed and is capable of transmitting data through a bluetooth ® transceiver 29 . the bluetooth transceiver 29 is connected to a bluetooth ® antenna 30 . a user or qualified physician who wishes to change the patient &# 39 ; s drug regimen from a remote location first sends the data to the patient . the sent information is then picked up by the bluetooth ® transceiver 29 and antenna 30 and is then stored on the flash memory chips 28 . when the drug delivery cpu 27 retrieves information from the flash memory chips 28 it adjusts the drug regimen ( dose , scheduling , etc .) according to the user &# 39 ; s data instructions . the external cpd 1 is capable of delivering up to four different drugs simultaneously with high accuracy in the following manner : the pump electronics assembly 12 of fig8 a comprises up to four piezoelectric pumps 17 driven by a corresponding ampoule pump integrated circuit 20 that together pump the medicating agent out of the ampoule 2 . the use and manufacture of piezo pumps are well known to those in the art . fewer or additional piezo pumps 17 than what is depicted in fig8 a may be used without departing from the original spirit and scope of the invention . the pump needles 18 are sufficiently long enough so that when a drug ampoule 2 is attached to the piezo pump 17 as depicted in fig2 , the medicating agent at the bottom of the ampoule may be accessed . pump needles 18 coupled to the piezoelectric pumps 17 penetrate the ampoules 2 and the piezoelectric pump 17 pumps the medicating agent through a drug manifold tube 24 and into a delivery valve 15 and out through the drug delivery connector 7 . the delivery valve 15 is regulated by a delivery valve driver integrated circuit 22 which is controlled by the drug delivery cpu 27 . the medicating agent , after being pumped through the delivery connector 7 , then enters into the delivery hose connector 37 ( fig5 ) via the drug output 4 on the delivery connector 7 depicted in fig4 b . the medicating agent is then pumped through the delivery hose 200 and into the cranial pump unit 100 via the seal connector 102 . in fig5 , the delivery hose 200 couples to the cpd 1 via a delivery hose connector 37 . the external cpd 1 is fully programmable and runs intelligent software to determine what and how much drug is required . the regulation loop of the intelligent drug delivery system uses a return sample of fluids from the “ delivery area ” to determine the necessary response . in fig5 , the return sample fluid obtained from the patient travels through the delivery hose 200 , through the delivery hose connector 37 , and then enters delivery connector 7 through the sample return 5 as shown in fig4 b . turning to fig8 a , after the sample fluid passes from the delivery connector 7 , the sample fluid enters the delivery valve 15 . the negative pressure necessary to pump the sample is created by the return piezoelectric pump 16 that is powered by a return pump driver integrated circuit 19 . the fluid sample then travels from the delivery valve 15 into a return pump input tube 25 and into a lab - on - a - chip 21 that senses the chemical composition of the sample . the return piezoelectric pump 16 continues pumping the sample fluid through itself and back out into a return output pump tube 23 . the sample fluid is then mixed together with the delivery drug in the delivery valve 15 , to continue a closed loop cycle to be returned to the collection site . the second main assembly , the induction charger assembly 11 , is depicted in greater detail in fig9 a and 9 b . the induction charger assembly 11 provides with a means for charging a lithium ion battery 14 ( shown in fig5 ). an induction coil 38 coupled to the induction charger electronics assembly 11 receives a high frequency ( 50 khz ) induced magnetic field from a similar charging coil from an external battery charger device ( not shown ). the induction coil 38 is coupled to a rectifier 35 shown in fig9 b . the rectifier 35 converts the high frequency voltage to a dc voltage that is filtered by an inductor 34 and capacitors 33 . a battery charger controller 32 regulates the charging of the battery 14 . the charger connector 36 is both for powering the electronics as well as charging the lithium ion battery 14 . the battery 14 is appropriately sized to provide sufficient power for days of service without the need of charging . the lithium ion battery 14 preferably has an “ l ” shape as shown in fig6 so as to leave sufficient space available for the pump needles 18 and drug ampoules 2 within the housing of the cpd 1 and is sized to provide sufficient power for days of service without the need of re - charging . however it is to be expressly understood that other varieties of batteries with various life spans and shapes may also be used without departing from the original scope and spirit of the invention . the lithium ion battery 14 is coupled directly to the housing of the cpd 1 and is removable so that when the stored energy has been depleted from the battery 14 , it may be easily replaced fig1 is a functional circuit diagram further illustrating the relationship between the elements of cpd 1 described above . many alterations and modifications may be made by those having ordinary skill in the art without departing from the spirit and scope of the invention . therefore , it must be understood that the illustrated embodiment has been set forth only for the purposes of example and that it should not be taken as limiting the invention as defined by the following invention and its various embodiments . for example , one skilled in t * e art may produce a device with fewer or additional drug ampoule bays or piezoelectric pumps without departing from the original scope and spirit of the invention . therefore , it must be understood that the illustrated embodiment has been set forth only for the purposes of example and that it should not be taken as limiting the invention as defined by the following claims . for example , notwithstanding the fact that the elements of a claim are set forth below in a certain combination , it must be expressly understood that the invention includes other combinations of fewer , more or different elements , which are disclosed in above even when not initially claimed in such combinations . a teaching that two elements are combined in a claimed combination is further to be understood as also allowing for a claimed combination in which the two elements are not combined with each other , but may be used alone or combined in other combinations . the excision of any disclosed element of the invention is explicitly contemplated as within the scope of the invention . the words used in this specification to describe the invention and its various embodiments are to be understood not only in the sense of their commonly defined meanings , but to include by special definition in this specification structure , material or acts beyond the scope of the commonly defined meanings . thus if an element can be understood in the context of this specification as including more than one meaning , then its use in a claim must be understood as being generic to all possible meanings supported by the specification and by the word itself . the definitions of the words or elements of the following claims are , therefore , defined in this specification to include not only the combination of elements which are literally set forth , but all equivalent structure , material or acts for performing substantially the same function in substantially the same way to obtain substantially the same result . in this sense it is therefore contemplated that an equivalent substitution of two or more elements may be made for any one of the elements in the claims below or that a single element may be substituted for two or more elements in a claim . although elements may be described above as acting in certain combinations and even initially claimed as such , it is to be expressly understood that one or more elements from a claimed combination can in some cases be excised from the combination and that the claimed combination may be directed to a subcombination or variation of a subcombination . insubstantial changes from the claimed subject matter as viewed by a person with ordinary skill in the art , now known or later devised , are expressly contemplated as being equivalently within the scope of the claims . therefore , obvious substitutions now or later known to one with ordinary skill in the art are defined to be within the scope of the defined elements . the claims are thus to be understood to include what is specifically illustrated and described above , what is conceptionally equivalent , what can be obviously substituted and also what essentially incorporates the essential idea of the invention .
a magnetically controlled pump is implanted into the brain of a patient and delivers a plurality of medicating agents at a controlled rate corresponding to the specific needs of the patient . the current invention comprises a flexible double walled pouch that is formed from two layers of polymer . the pouch is alternately expanded and contracting by magnetic solenoid . when contracted , a medicating agent is pushed out of the pouch through a plurality of needles . when the pouch is expanded , surrounding cerebral fluid is drawn into the space between the double walls of the pouch from which it is drawn through a catheter to an analyzer . cerebral fluid drawn from the patient is analyzed . the operation of the apparatus and hence the treatment is remotely controlled based on these measurements and displayed through an external controller .