to provide vagal blocking and / or vagal stimulation therapy to a patient , blocking and stimulation electrodes are implanted at the appropriate sites . in one preferred embodiment , without limitation , multiple electrodes comprising both blocking and stimulation electrodes are placed in a band . as shown in conjunction with fig1 , the band comprising multiple electrodes is wrapped around the esophagus , close to the junction of esophagus and the stomach 5 ( just below the diaphragm ). alternatively , the individual electrodes do not have to be in a band , and may be individual electrodes , connected to the body of the lead via insulated conductors . in such a case , the portion of the electrode contacting the nerve tissue would be exposed and the rest of the electrode being insulated with a non - conductive material such as silicone or polyurethane . such electrodes are well known in the art . the electrodes may be implanted using laproscopic surgery or alternatively a surgical exposure may be made for implantation of the electrodes at the appropriate site to be stimulated and / or blocked . after placing the electrodes , the terminal portion of the lead is tunneled to a subcutaneous site where the electronics package is to be implanted . the terminal end of the lead is connected to the stimulus - receiver or the implanted stimulator . the patient is surgically closed , and electrical pulse delivery can begin once the patient has fully recovered from the surgery . in the method and system of this invention , stimulation without block may be provided . additionally , stimulation with selective block may be provided . furthermore , block alone ( without stimulation ) may be provided , which would be functionally equivalent to reversible vagotomy . blocking of nerve impulses , unidirectional blocking , and selective blocking of nerve impulses is well known in the scientific literature . some of the general literature is listed below and is incorporated herein by reference . ( a ) “ generation of unidirectionally propagating action potentials using a monopolar electrode cuff ”, annals of biomedical engineering , volume 14 , pp . 437 - 450 , by ira j . ungar et al . ( b ) “ an asymmetric two electrode cuff for generation of unidirectionally propagated action potentials ”, ieee transactions on biomedical engineering , volume bme - 33 , no . 6 , june 1986 , by james d . sweeney , et al . ( c ) a spiral nerve cuff electrode for peripheral nerve stimulation , ieee transactions on biomedical engineering , volume 35 , no . 11 , november 1988 , by gregory g . naples . et al . ( d ) “ a nerve cuff technique for selective excitation of peripheral nerve trunk regions , ieee transactions on biomedical engineering , volume 37 , no . 7 , july 1990 , by james d . sweeney , et al . ( e ) “ generation of unidirectionally propagated action potentials in a peripheral nerve by brief stimuli ”, science , volume 206 pp . 1311 - 1312 , dec . 14 , 1979 , by van den honert et al . ( f ) “ a technique for collision block of perpheral nerve : frequency dependence ” ieee transactions on biomedical engineering , mp - 12 , volume 28 , pp . 379 - 382 , 1981 , by van den honert et al . ( g ) “ a nerve cuff design for the selective activation and blocking of myelinated nerve fibers ” ann . conf . of the ieee engineering in medicine and biology soc ., volume 13 , no . 2 , p 906 , 1991 , by d . m fitzpatrick et al . ( h ) “ orderly recruitment of motoneurons in an acute rabbit model ”, “ ann . conf . of the ieee engineering in medicine and biology soc ., volume 20 , no . 5 , page 2564 , 1998 , by n . j . m . rijkhof , et al . ( i ) “ orderly stimulation of skeletal muscle motor units with tripolar nerve cuff electrode ”, ieee transactions on biomedical engineering , volume 36 , no . 8 , pp . 836 , 1989 , by r . bratta . ( j ) m . devor , “ pain networks ”, handbook of brand theory and neural networks , ed . m . a . arbib , mit press , page 698 , 1998 . blocking can be generally divided into 3 categories : ( a ) dc or anodal block , ( b ) wedenski block , and ( c ) collision block . in anodal block there is a steady potential which is applied to the nerve causing a reversible and selective block . in wedenski block the nerve is stimulated at a high rate causing the rapid depletion of the neurotransmitter . in collision blocking , unidirectional action potentials are generated anti - dromically . the maximal frequency for complete block is the reciprocal of the refractory period plus the transit time , i . e . typically less than a few hundred hertz . the use of any of these blocking techniques can be applied for the practice of this invention , and all are considered within the scope of this invention . for supplying the electrical signals , two embodiments are disclosed for carrying out the invention . in the first embodiment the implanted stimulus - receiver is a simpler device comprising an implanted secondary coil along with the associated circuitry . in the second embodiment , the implanted unit also comprises a high value capacitor ( supercap ) for storing charge for up to a few hours . in both embodiments , the initial power is supplied from an external unit via an external ( primary ) coil . in the first embodiment , for therapy to commence , the primary ( external ) coil 46 is placed on the skin 60 on top of the surgically implanted ( secondary ) coil 48 . an adhesive tape may be placed on the skin 60 and external coil 46 such that the external coil 46 , is taped to the skin 60 . alternatively , a special garment may be used for the placement of the primary ( external ) coil , or other means may be used . shown in conjunction with fig1 , 20 and 21 , the external stimulator 42 is adapted to inductively couple with an implanted stimulus - receiver 34 . the primary ( external ) coil 46 of the external pulse generator 42 inductively transfers pulses to the implanted stimulus - receiver 34 , which has multiple electrodes ( via the lead ) in contact with the appropriate nerve tissue for vagal blocking and / or stimulation . when the two coils , which are the primary coil 46 ( external ) and secondary coil 48 ( implanted ) are arranged with their axes on the same line , current sent through coil 46 creates a magnetic field that cuts coil 48 which is subcutaneous . consequently , a voltage will be induced in the secondary coil 48 whenever the field strength of the primary coil 46 is changing . this induced voltage is similar to the voltage of self - induction but since it appears in the second coil because of current flowing in the first , it is a mutual effect and results from the mutual inductance between the two coils ( primary 46 and secondary 48 ). the degree of coupling of these two coils depends upon the physical spacing between the coils and how they are placed with respect to each other . maximum coupling exists when they have a common axis and are as close together as possible ( but separated by skin 60 ). the coupling is least when the coils are far apart or are placed so their axes are at right angles . as depicted in fig2 and 21 , the secondary coil 48 inside the stimulus - receiver 34 is approximately along the same axis as the primary coil 46 . fig2 shows a schematic diagram of an implantable stimulus - receiver 34 . the stimulus - receiver receives the pulses from outside the body . the proximal end of the stimulus - receiver 34 comprises the secondary coil 48 and electronic circuitry ( hybrid ) 167 which is hermetically sealed , and covered with silicone . it may have one or more anchoring sleeve ( s ) 130 for tying it to the subcutaneous tissue . fig2 shows in block diagram form , the delivery methodology to deliver vagal blocking and / or stimulation pulses . a modulator 246 receives analog ( sine wave ) high frequency “ carrier ” signal and modulating signal . the modulating signal can be multilevel digital , binary , or even an analog signal . in this embodiment , mostly multilevel digital type i . e ., pulse amplitude and pulse width modulated signals are used . the modulated signals are conditioned 248 , amplified 250 , and transmitted via a primary coil 46 which is external to the body . shown in conjunction with fig2 , a secondary coil 48 of the implanted stimulus - receiver , receives , demodulates , and delivers these pulses to the vagal tissue 54 . the receiver circuitry 256 is described later . the carrier frequency is optimized . one preferred embodiment utilizes electrical signals of around 1 mega - hertz , even though other frequencies can be used . low frequencies are generally not suitable because of energy requirements for longer wavelengths , whereas higher frequencies are absorbed by the tissues and are converted to heat , which again results in power losses . the implantable stimulus - receiver 34 has circuitry at the proximal end , and has stimulating and blocking electrodes at the distal end of the lead . the circuitry contained in the proximal end of the implantable stimulus - receiver 34 is shown schematically in fig2 , for one embodiment . in this embodiment , the circuit uses all passive components . approximately 25 turn copper wire of 30 gauge , or comparable thickness , is used for the primary coil 46 and secondary coil 48 . other functional equivalents may also be used . this wire is concentrically wound with the windings all in one plane . the frequency of the pulse - waveform delivered to the implanted coil 48 can vary , and so a variable capacitor 152 provides ability to tune secondary implanted circuit 167 to the signal from the primary coil 46 . the pulse signal from secondary ( implanted ) coil 48 is rectified by the diode bridge 154 and frequency reduction obtained by capacitor 158 and resistor 164 . the last component in line is capacitor 166 , used for isolating the output signal from the electrode wire . for stimulation / blocking signals , the return path of signals from cathode 61 will be through anode 62 placed in proximity to the cathode 61 for “ bipolar ” stimulation . in this embodiment bipolar mode of stimulation is used , however , the return path can be connected to the remote ground connection ( case ) of implantable circuit 167 , providing for much larger intermediate tissue for “ unipolar ” stimulation . the “ bipolar ” stimulation offers localized stimulation of tissue compared to “ unipolar ” stimulation and is therefore , preferred in this embodiment . the implanted circuit 167 in this embodiment is passive , so a battery does not have to be implanted . the circuitry shown in fig2 and 26 can be used as an alternative for the implanted stimulus - receiver 34 . the circuitry of fig2 is a slightly simpler version , and circuitry of fig2 contains a conventional npn transistor 168 connected in an emitter - follower configuration . for efficient energy transfer to occur , it is important that the primary ( external ) 46 and secondary ( implanted ) coils 48 be positioned along the same axis and be optimally positioned relative to each other . in this embodiment , the external coil 46 may be connected to proximity sensing circuitry 50 . the correct positioning of the external coil 46 with respect to the implanted coil 48 is indicated by turning “ on ” of a light emitting diode ( led ) on the external stimulator 42 . many different forms of proximity sensing mechanisms may be used . in one embodiment optimal placement of the external ( primary ) coil 46 may be done with the aid of proximity sensing circuitry incorporated in the system . proximity sensing occurs utilizing a combination of external and implantable components . the implanted components contains a relatively small magnet composed of materials that exhibit giant magneto - resistor ( gmr ) characteristics such as samarium - cobalt , a coil , and passive circuitry . as was depicted in conjunction with fig2 , the external coil 46 and proximity sensor circuitry 50 are rigidly connected in a convenient enclosure which is attached externally on the skin . the sensors measure the direction of the field applied from the magnet to sensors within a specific range of field strength magnitude . the dual sensors exhibit accurate sensing under relatively large separation between the sensor and the target magnet . as the external coil 46 placement is “ fine tuned ”, the condition where the external ( primary ) coil 46 comes in optimal position , i . e . is located adjacent and parallel to the subcutaneous ( secondary ) coil 48 , along its axis , is recorded and indicated by a light emitting diode ( led ) on the external stimulator 42 . other forms of proximity sensing mechanisms may also be used fig2 shows a front view of one embodiment of an external stimulator 42 . the external stimulator 42 contains the circuitry , rechargeable power source , external coil and , an optional telemetry module . fig2 shows a block diagram of the external stimulator 42 . the pre - packaged or “ customized ” programs are stored in the memory unit 71 . this represents memory with a readable and writeable portion and a non - volatile pre - programmable portion . a field programmable array unit ( fpga ) 75 and a random access component ( ram ) 320 and random addressable storage logic 340 , facilitates application of logic to edit and change the “ current ” parameters being utilized for pulse generation . the programmable unit interface 323 provides an interface to a programming unit ( portable computer system ) 77 , which allows re - loading of a new set of programs . the pulse generation component 79 generates pulses of well - defined parameters , selected from the programmed parameters that exist in the memory unit 71 . the pulse signal generation unit 79 provides its signal to be amplified and conditioned at the amplifier and signal conditioning unit 83 which then provides these signals to the primary ( external ) inductive coil 46 . the logic and control unit can provide both the blocking and stimulating pulses . in one embodiment a pair of sensors 174 senses the position of the implanted magnet 53 and the sensor signal is fed back to the proximity sensor control block 208 via the feedback signal conditioning unit 209 . the feedback signal provides a proportional signal for modification of the frequency , amplitude and pulse - width of the pulse being generated by the pulse signal generator unit 79 . the sensor unit has two sensors 171 , 173 that sense the location of the implanted magnet 53 . the implanted ( secondary ) coil 48 is rigidly connected to the passive circuit and magnet 53 . the skin 60 separates the subcutaneous and external components . the external components are placed on the skin , with the primary coil 46 in close proximity and optimally situated with respect to the implanted ( secondary ) coil 48 . as is shown in conjunction with fig2 and fig3 , the external pulse generator 42 is composed of three modules or sub - assemblies . the first sub - assembly is the pulse generation and signal conditioning components 196 , the second is the battery 81 , and the third is the telemetry and memory unit 180 . the presently preferred embodiment , comprises proximity sensing and feedback circuitry . this invention can be practiced without the proximity sensing and feedback circuitry . the pulse generator is able to function as supplier of electric pulses to the nerve tissue without the proximity feedback loop and the telemetry module . these modules or sub - assemblies also provide for a scalable external pulse generator 42 . in the telemetry module , a wireless antenna 182 provides a means of communication to the external pulse generator 42 and the wireless remote server 189 . a programming unit 77 can also be physically connected to the external stimulator 42 ( via the programming unit interface 323 ) in a tethered manner for loading of new programs or changing parameters of an existing program . fig2 shows the programmable array logic and interface unit 75 interfaced to the programming station 77 . the programming station allows the user to change the program parameters for various stimulation and / or blocking programs . the programming station is connected to the programmable array unit 75 with an rs232 - c serial connection 324 . the main purpose of the serial line interface is to provide an rs232 - c standard interface . this method enables any portable computer with a serial interface to communicate and program the parameters for storing the various programs . the serial communication interface 323 receives the serial data , buffers this data and converts it to a 16 bit parallel data . the programmable array logic 320 component of programmable array unit 75 receives the parallel data bus and stores or modifies the data into a random access matrix . this array of data also contains special logic and instructions along with the actual data . these special instructions also provide an algorithm for storing , updating and retrieving the parameters from long - term memory . the programmable array unit 320 , interfaces with long term memory 71 to store the pre - determined programs . all the previously modified programs can be stored here for access at any time . the programs will consist of specific parameters and each unique program will be stored sequentially in long term memory 71 . a battery unit 81 provides power to all the components shown above . the logic for the storage and decoding is stored in the random addressable storage matrix ( rasm ) 340 ( fig3 ). fig3 shows greater details for the programmable logic array unit 320 . the input buffer block 343 stores the serial data in temporary register storage . this accumulation allows for the serial to parallel conversion to occur . the serial to 16 bit parallel block sets up 16 bits of data 346 , as created from the rs232 - c serial data . this parallel data bus will communicate the data and the address information . the decoder block 344 decodes address information for the random addressable logic storage matrix 340 from which to access the data i . e . programmer parameters . the output buffer 342 provides an interface to the long term memory 71 . fig3 shows schematically the details of the interface between the programmable array logic 320 and interface unit 75 which is connected to the predetermined programs block ( long term memory ) 71 . the patient override 73 is essentially a control scheme for initializing or starting a program at any intermediate point . the field programmable array provides a reconfigurable mechanism to store data and associated instructions for the programs . it supports adding , modifying or retrieving the data from a random addressable logic storage matrix 340 . this is also a scheme for treating “ flexible ” logic description and control . it is flexible by providing the ability to reprogram and even redesign existing programs previously installed programs . as was shown schematically in fig2 , the health care provider can load and reload stimulation programs of choice . this allows the authorized user to create , modify and select for execution , programs to use for a particular time period . fig3 shows an example of pulse generator circuitry , which exhibits typical multivibrator functionality . it will be clear to one skilled in the art , that other circuits can also be used . this circuit produces regularly occurring pulses where the amplitude , pulse width and frequency is adjustable . the battery 81 is the main external power source for this circuit . the capacitor 250 is connected in parallel with the battery 81 . the combination of transistors 212 , 242 and 225 , and resistors 210 , 244 , 246 and 248 acts as a constant current source generated at the collector of transistor 226 . the transistor 212 has collector connected to the emitter of transistor 242 and base of transistor 225 . the transistors 212 and 242 are connected to provide a constant voltage drop . likewise , transistor 226 also acts as a diode with a resistor 228 connected in series and further connected to the negative terminal of the line at terminal 260 . capacitor 216 provides timing characteristics and its value helps determine pulse width and pulse frequency . the output of the oscillator appears at terminal 258 . initially , the capacitor 216 gets charged with current from the path of resistor 234 and 236 while all the transistors are turned off . as the capacitor charges up transistor 232 will become forward biased and current will flow via resistors 230 and 236 from the base to emitter resistors . this action turns on the transistor 218 and the positive voltage from the power supply 81 is made available at the base of transistor 238 through resistor 240 . this results in the transistor 238 getting turned on . the conduction of transistor 238 causes capacitor 216 to discharge . the time constant for the charge and discharge of capacitor 216 is determined by value of the resistors 228 and 240 and capacitor 216 . after the time constant , transistor 232 turns off , and this in turn turns off transistors 238 and 218 . a reset mechanism for this multivibrator can be provided by setting a positive voltage , for example 2 . 5 volts , to the base of transistor 220 . this positive increase in voltage turns on transistor 220 followed by transistor 238 . the turning on of transistor 238 discharges the capacitor 216 and the reset operation is complete . conventional integrated circuits are used for the logic , control and timing circuits . conventional bipolar transistors are used in radio - frequency oscillator , pulse amplitude ramp control and power amplifier . a standard voltage regulator is used in low - voltage detector . the hardware and software to deliver these pre - determined programs is well known to those skilled in the art . the selective blocking and / or stimulation to the vagal nerve tissue can be performed by “ pre - determined ” programs or by “ customized ” programs , where the electrical parameters are selectively programmed , for specific therapy to the individual patient . the electrical parameters which can be individually programmed , include variables such as pulse amplitude , pulse width , frequency of stimulation , type of pulse ( e . g . blocking pulses may be sinusoidal ), stimulation on - time , and stimulation off - time . table two below defines the approximate range of parameters , table 2 -- electrical parameter range delivered to the nerve for stimulation and / or blocking the parameters in table 2 are the electrical signals delivered to the nerve tissue via the two stimulation electrodes 61 , 62 ( or blocking electrodes ) at the nerve tissue . it being understood that the signals generated by the external pulse generator 42 and transmitted via the primary coil 46 are larger , because the attenuation factor between the primary coil and secondary coil is approximately 10 - 20 times , depending upon the distance , and orientation between the two coils . accordingly , the range of transmitted signals of the external pulse generator 42 are approximately 10 - 20 times larger than shown in table 2 . the implanted lead component of the system is somewhat similar to cardiac pacemaker leads , except for distal portion 40 ( or electrode end ) of the lead . the lead terminal preferably is linear , even though it can be bifurcated , and plug ( s ) into the cavity of the pulse generator means . the lead body 59 insulation may be constructed of medical grade silicone , silicone reinforced with polytetrafluoro - ethylene ( ptfe ), or polyurethane . the stimulation electrodes 61 , 62 ( or blocking electrodes ) are typically implanted adjacent to the nerve tissue to be stimulated or blocked . the electrodes may be made of pure platinum , platinum / iridium alloy or platinum / iridium coated with titanium nitride . the conductor connecting the terminal to the electrodes is made of an alloy of nickel - cobalt . the implanted lead design variables are also summarized in table three below . in one embodiment , the implanted stimulus - receiver may be a system which is rf coupled combined with a power source . in this embodiment , the implanted stimulus - receiver also comprises high value , small sized capacitor ( s ) for storing charge and delivering electric stimulation and / or blocking pulses for up to several hours by itself , once the capacitors are charged . the packaging is shown in fig3 . using mostly hybrid components and appropriate packaging , the implanted portion of the system described below is conducive to miniaturization . as shown in fig3 , a solenoid coil 382 wrapped around a ferrite core 380 is used as the secondary of an air - gap transformer for receiving power and data to the implanted device . the primary coil is external to the body . since the coupling between the external transmitter coil and receiver coil 382 may be weak , a high - efficiency transmitter / amplifier is used in order to supply enough power to the receiver coil 382 . class - d or class - e power amplifiers may be used for this purpose . the coil for the external transmitter ( primary coil ) may be placed in the pocket of a customized garment . shown in conjunction with fig3 of the implanted stimulus - receiver 490 and the system , the receiving inductor 48 a and tuning capacitor 403 are tuned to the frequency of the transmitter . the diode 408 rectifies the ac signals , and a small sized capacitor 406 is utilized for smoothing the input voltage v i fed into the voltage regulator 402 . the output voltage v d of regulator 402 is applied to capacitive energy power supply and source 400 which establishes source power v dd . capacitor 400 is a big value , small sized capacative energy source which is classified as low internal impedance , low power loss and high charge rate capacitor , such as panasonic model no . 641 ( available from pansonic corporation ). the refresh - recharge transmitter unit 460 includes a primary battery 426 , an on / off switch 427 , a transmitter electronic module 442 , an rf inductor power coil 46 a , a modulator / demodulator 420 and an antenna 422 . when the on / off switch is on , the primary coil 46 a is placed in close proximity to skin 60 and secondary coil 48 a of the implanted stimulator 490 . the inductor coil 46 a emits rf waves establishing emf wave fronts which are received by secondary inductor 48 a . further , transmitter electronic module 424 sends out command signals which are converted by modulator / demodulator decoder 420 and sent via antenna 422 to antenna 418 in the implanted stimulator 490 . these received command signals are demodulated by decoder 416 and replied and responded to , based on a program in memory 414 ( matched against a “ command table ” in the memory ). memory 414 then activates the proper controls and the inductor receiver coil 48 a accepts the rf coupled power from inductor 46 a . the rf coupled power , which is alternating or ac in nature , is converted by the rectifier 408 into a high dc voltage . small value capacitor 406 operates to filter and level this high dc voltage at a certain level . voltage regulator 402 converts the high dc voltage to a lower precise dc voltage while capacitive power source 400 refreshes and replenishes . when the voltage in capacative source 400 reaches a predetermined level ( that is vdd reaches a certain predetermined high level ), the high threshold comparator 430 fires and stimulating electronic module 412 sends an appropriate command signal to modulator / decoder 416 . modulator / decoder 416 then sends an appropriate “ fully charged ” signal indicating that capacitive power source 400 is fully charged , is received by antenna 422 in the refresh - recharge transmitter unit 460 . in one mode of operation , the patient may start or stop stimulation / blocking by waving the magnet 442 once near the implant . the magnet emits a magnetic force l m which pulls reed switch 410 closed . upon closure of reed switch 410 , stimulation / blocking electronic module 412 in conjunction with memory 414 begins the delivery ( or cessation as the case may be ) of controlled electronic stimulation / blocking pulses to the nerve tissues via the implanted electrodes . in another mode ( auto ), the stimulation / blocking is automatically delivered to the implanted lead based upon programmed on / off times . the programmer unit 450 includes keyboard 432 , programming circuit 438 , rechargeable battery 436 , and display 434 . the physician or medical technician programs programming unit 450 via keyboard 432 . this program regarding the frequency , pulse width , modulation program , on time etc . is stored in programming circuit 438 . the programming unit 450 must be placed relatively close to the implanted stimulator 490 in order to transfer the commands and programming information from antenna 440 to antenna 418 . upon receipt of this programming data , modulator / demodulator and decoder 416 decodes and conditions these signals , and the digital programming information is captured by memory 414 . this digital programming information is further processed by stimulation / blocking electronic module 412 . in the demand operating mode , after programming the implanted stimulator , the patient turns on and off the implanted stimulator via hand held magnet 442 and the reed switch 410 . in the automatic mode ( auto ), the implanted stimulator turns on and off automatically according to the programmed values for the on and off times . other simplified versions of such a system may also be used . for example , a system such as this , where a separate programmer is eliminated , and simplified programming is performed with a magnet and reed switch , can also be used . it will be clear from the above disclosure that the implanted stimulus - receiver may be purely a passive device or may comprise a power source , such as a high value capacitor . in either case , initially the energy provided via an external stimulator 42 . shown in conjunction with fig3 , in one embodiment of the invention the external pulse generator 42 has two - way wireless communication capabilities with a remote server , using a communication protocol such as the wireless application protocol ( wap ). the purpose of the telemetry module is to enable the physician to remotely , via the wireless medium change the programs , activate , or disengage programs . additionally , schedules of therapy programs , can be remotely transmitted and verified . advantageously , the physician is thus able to remotely control the stimulation therapy . fig3 is a simplified schematic showing the communication aspects between the pulse generator 42 and the remote hand - held computer . a desktop or laptop computer can be a server 130 which is situated remotely , perhaps at a health - care provider &# 39 ; s facility or a hospital . the data can be viewed at this facility or reviewed remotely by medical personnel on a wireless internet supported hand - held device 140 , which could be a personal data assistant ( pda ), for example , a “ palm - pilot ” from palm corp . ( santa clara , calif . ), a “ visor ” from handspring corp . ( mountain view , calif .) or on a personal computer ( pc ) available from numerous vendors or a cell phone or a handheld device being a combination thereof . the physician or appropriate medical personnel , is able to interrogate the external stimulator 42 device and know what the device is currently programmed to , as well as , get a graphical display of the pulse train . the wireless communication with the remote server 130 and hand - held device ( wireless internet supported ) 140 can be achieved in all geographical locations within and outside the united states ( us ) that provides cell phone voice and data communication service . the pulse generation parameter data can also be viewed on the handheld devices 140 . the telecommunications component of this invention uses wireless application protocol ( wap ). wap is a set of communication protocols standardizing internet access for wireless devices . previously , manufacturers used different technologies to get internet on hand - held devices . with wap , devices and services inter - operate . wap promotes convergence of wireless data and the internet . the wap layers are wireless application envirnment ( waew ), wireless session layer ( wsl ), wireless transport layer security ( wtls ) and wireless transport layer ( wtp ). the wap programming model , which is heavily based on the existing internet programming model , is shown schematically in fig3 . introducing a gateway function provides a mechanism for optimizing and extending this model to match the characteristics of the wireless environment . over - the - air traffic is minimized by binary encoding / decoding of web pages and readapting the internet protocol stack to accommodate the unique characteristics of a wireless medium such as call drops . such features are facilitated with wap . the key components of the wap technology , as shown in fig3 , includes 1 ) wireless mark - up language ( wml ) 400 which incorporates the concept of cards and decks , where a card is a single unit of interaction with the user . a service constitutes a number of cards collected in a deck . a card can be displayed on a small screen . wml supported web pages reside on traditional web servers . 2 ) wml script which is a scripting language , enables application modules or applets to be dynamically transmitted to the client device and allows the user interaction with these applets . 3 ) microbrowser , which is a lightweight application resident on the wireless terminal that controls the user interface and interprets the wml / wmlscript content . 4 ) a lightweight protocol stack 402 which minimizes bandwidth requirements , guaranteeing that a broad range of wireless networks can run wap applications . the protocol stack of wap can comprise a set of protocols for the transport ( wtp ), session ( wsp ), and security ( wtls ) layers . wsp is binary encoded and able to support header caching , thereby economizing on bandwidth requirements . wsp also compensates for high latency by allowing requests and responses to be handles asynchronously , sending before receiving the response to an earlier request . for lost data segments , perhaps due to fading or lack of coverage , wtp only retransmits lost segments using selective retransmission , thereby compensating for a less stable connection in wireless . the above mentioned features are industry standards adopted for wireless applications , and well known to those skilled in the art . the presently preferred embodiment utilizes wap , because wap has the following advantages , 1 ) wap protocol uses less than one - half the number of packets that the standard http or tcp / ip internet stack uses to deliver the same content . 2 ) addressing the limited resources of the terminal , the browser , and the lightweight protocol stack are designed to make small claims on cpu and rom . 3 ) binary encoding of wml and smlscript helps keep the ram as small as possible . and , 4 ) keeping the bearer utilization low takes account of the limited battery power of the terminal . in this embodiment two modes of communication are possible . in the first , the server initiates an upload of the actual parameters being applied to the patient , receives these from the stimulator , and stores these in its memory , accessible to the authorized user as a dedicated content driven web page . the web page is managed with adequate security and password protection . the physician or authorized user can make alterations to the actual parameters , as available on the server , and then initiate a communication session with the stimulator device to download these parameters . the physician is also able to set up long - term schedules of stimulation therapy for their patient population , through wireless communication with the server . the server in turn communicates these programs to the neurostimulator . each schedule is securely maintained on the server , and is editable by the physician and can get uploaded to the patient &# 39 ; s stimulator device at a scheduled time . thus , therapy can be customized for each individual patient . each device issued to a patient has a unique identification key in order to guarantee secure communication between the wireless server 130 and stimulator device 42 . in this embodiment , two modes of communication are possible . in the first , the server initiates an upload of the actual parameters being applied to the patient , receives these from the stimulator , and stores these in its memory , accessible to the authorized user as a dedicated content driven web page . the physician or authorized user can make alterations to the actual parameters , as available on the server , and then initiate a communication session with the stimulator device to download these parameters . shown in conjunction with fig3 , in one embodiment , the external stimulator 42 and / or the programmer 85 may also be networked to a central collaboration computer 286 as well as other devices such as a remote computer 294 , pda 140 , phone 141 , physician computer 143 . the interface unit 292 in this embodiment communicates with the central collaborative network 290 via land - lines such as cable modem or wirelessly via the internet . a central computer 286 which has sufficient computing power and storage capability to collect and process large amounts of data , contains information regarding device history and serial number , and is in communication with the network 290 . communication over collaboration network 290 may be effected by way of a tcp / ip connection , particularly one using the internet , as well as a pstn , dsl , cable modem , lan , wan or a direct dial - up connection . the standard components of interface unit shown in block 292 are processor 305 , storage 310 , memory 308 , transmitter / receiver 306 , and a communication device such as network interface card or modem 312 . in the preferred embodiment these components are embedded in the external stimulator 42 and can also be embedded in the programmer 85 . these can be connected to the network 290 through appropriate security measures ( firewall ) 293 . another type of remote unit that may be accessed via central collaborative network 290 is remote computer 294 . this remote computer 294 may be used by an appropriate attending physician to instruct or interact with interface unit 292 , for example , instructing interface unit 292 to send instruction downloaded from central computer 286 to remote implanted unit . shown in conjunction with fig3 the physician &# 39 ; s remote communication &# 39 ; s module is a modified pda / phone 140 in this embodiment . the modified pda / phone 140 is a microprocessor based device as shown in a simplified block diagram in fig3 and 40 . the pda / phone 140 is configured to accept pcm / cia cards specially configured to fulfill the role of communication module 292 of the present invention . the modified pda / phone 140 may operate under any of the useful software including microsoft window &# 39 ; s based , linux , palm os , java os , symbian , or the like . the telemetry module 362 comprises an rf telemetry antenna 142 coupled to a telemetry transceiver and antenna driver circuit board which includes a telemetry transmitter and telemetry receiver . the telemetry transmitter and receiver are coupled to control circuitry and registers , operated under the control of microprocessor 364 . similarly , within stimulator a telemetry antenna 142 is coupled to a telemetry transceiver comprising rf telemetry transmitter and receiver circuit . this circuit is coupled to control circuitry and registers operated under the control of microcomputer circuit . with reference to the telecommunications aspects of the invention , the communication and data exchange between modified pda / phone 140 and external stimulator 42 operates on commercially available frequency bands . the 2 . 4 - to - 2 . 4853 ghz bands or 5 . 15 and 5 . 825 ghz , are the two unlicensed areas of the spectrum , and set aside for industrial , scientific , and medical ( ism ) uses . most of the technology today including this invention , use either the 2 . 4 or 5 ghz radio bands and spread - spectrum technology . the telecommunications technology , especially the wireless internet technology , which this invention utilizes in one embodiment , is constantly improving and evolving at a rapid pace , due to advances in rf and chip technology as well as software development . therefore , one of the intents of this invention is to utilize “ state of the art ” technology available for data communication between modified pda / phone 140 and external stimulator 42 . the intent of this invention is to use 3g technology for wireless communication and data exchange , even though in some cases 2 . 5g is being used currently . for the system of the current invention , the use of any of the “ 3g ” technologies for communication for the modified pda / phone 140 , is considered within the scope of the invention . further , it will be evident to one of ordinary skill in the art that as future 4 g systems , which will include new technologies such as improved modulation and smart antennas , can be easily incorporated into the system and method of current invention , and are also considered within the scope of the invention .
method and system to provide therapy for obesity and gastrointestinal disorders such as fgids , gastroparesis , gastro - esophageal reflex disease , pancreatitis and ileus comprises vagal blocking and / or vagal stimulation . vagal blocking may be in the afferent or efferent direction , and may be with or without stimulation pulses . blocking may be provided by one of a number of different electrical blocking techniques . electrical signals may be provided with an external stimulator in conjunction with an implanted stimulus - receiver , or an implanted stimulus - receiver comprising a high value capacitor for temporary power source . in one embodiment , the external stimulator may comprise an optional telemetry unit . the addition of the telemetry unit to the external stimulator provides the ability to remotely interrogate and change stimulation programs over a wide area network , as well as other networking capabilities ,