a dispensing unit ( 10 ) and a remote control unit ( 40 ) are described herein . in some embodiments , the dispensing unit ( 10 ) may include a single part ( as shown in fig1 b ) or two parts ( as shown in fig1 c ). the two - part dispensing unit includes a reusable part ( 100 ) and a disposable part ( 200 ). the dispensing unit ( 10 ) may employ different dispensing mechanisms , including without limitation a syringe - type reservoir with a propelling plunger , peristaltic positive displacement pump in some embodiments , the dispensing unit ( 10 ) can be adhered to the patient &# 39 ; s body by a skin adherable cradle unit . an example of such a cradle unit is disclosed in the co - owned , co - pending u . s . patent application ser . no . 12 / 004 , 837 and international patent application no . pct / il2007 / 001578 , the disclosures of which are incorporated herein by reference in their entireties . the term “ dispensing unit ” is not limited to fluid delivery . in some embodiments , the dispensing unit ( 10 ) may be capable of dispensing fluid ( e . g ., insulin ) to a patient &# 39 ; s body or sensing analyte ( e . g ., glucose ) in the body . infusion programming , data transferring and control of the dispensing unit ( 10 ) can be carried out by a remote control unit ( 40 ), which may be configured as a personal digital assistant (“ pda ”), a hand watch , a cellular phone , or any other means . the remote control unit ( 40 ) is capable of establishing a unidirectional communication with the dispensing unit ( 10 ), i . e ., the remote control unit ( 40 ) only transmits data to the dispensing unit ( 10 ) or only receives data from the dispensing unit ( 10 ). the communication link between remote control unit ( 40 ) and dispensing unit ( 10 ) can be also bidirectional , i . e ., the remote control unit ( 40 ) is capable of transmitting and receiving data to and from the dispensing unit ( 10 ). fig2 a - b show exemplary embodiments of the dispensing unit ( 10 ) employing a peristaltic pumping mechanism for dispensing fluid to a user &# 39 ; s body . fig2 a shows a single - part dispensing unit ( 10 ). the fluid is delivered from a reservoir ( 220 ) provided in the dispensing unit ( 10 ) through a delivery tube ( 230 ) to an exit port ( 213 ). the peristaltic pump includes a rotary wheel ( 110 ) provided with rollers ( not shown ) and a stator ( 190 ). rotation of the rotary wheel ( 110 ) and periodic squeezing of the delivery tube ( 230 ) against the stator ( 190 ) positively displaces fluid from the reservoir ( 220 ) to the exit port ( 213 ). an example of such a positive displacement pump is disclosed in the co - owned , co - pending u . s . patent application ser . no . 11 / 397 , 115 , filed on apr . 3 , 2006 , the disclosure of which is incorporated herein by reference in its entirety . a driving mechanism ( 120 ) for rotating the rotary wheel ( 110 ) can be provided . the driving mechanism ( 120 ) includes a gear and a motor . the motor can be a stepper motor , a dc motor , sma actuator or any other motor . the driving mechanism ( 120 ) is controlled by electronic components ( 130 ) residing in the dispensing unit ( 10 ). the electronic components ( 130 ) may include a controller ( not shown ), a processor ( 132 ), a transceiver ( 131 ) and / or a transmitter ( 133 ). an appropriate power source ( 240 ) and an energy storage device ( 252 ) ( e . g ., a capacitor ) are also provided . the power source ( 240 ) may include without limitation one or more batteries , such as a button - sized zinc - air battery . in some embodiments , the power source ( 240 ) may be a button battery and the energy storage device ( 252 ) may be a high capacity ( e . g ., about 0 . 2 f ) capacitor . using a button battery usually requires the supply of pulsed power in order to increase the current output by the battery . the pulsed power mode is established by periodically charging and discharging the high capacity capacitor . infusion programming of the dispensing unit ( 10 ) can be carried out either by remote control unit ( 40 ) and / or by manual buttons ( 15 ) provided on the dispensing unit ( 10 ). fig2 b shows a two - part dispensing unit ( 10 ) that includes a reusable part ( 100 ) and a disposable part ( 200 ). the reusable part ( 100 ) includes a positive displacement pump provided with rotary wheel ( 110 ), driving mechanism ( 120 ), and electronic components ( 130 ). the disposable part ( 200 ) includes reservoir ( 220 ), delivery tube ( 230 ), power source ( e . g ., button battery ) ( 240 ), energy storage device ( 252 ), exit port ( 213 ), and stator ( 190 ). pumping is enabled upon attachment of the two parts to each other . this arrangement is discussed in the co - owned , co - pending u . s . patent application ser . no . 11 / 397 , 115 , filed on apr . 3 , 2006 , the disclosure of which is incorporated herein by reference in its entirety . the power source ( 240 ) may also be located in the reusable part ( 100 ) and can be rechargeable . fig3 a and 3 b show respectively an embodiment of the two - part dispensing unit ( 10 ) prior to ( as shown in fig3 a ) and subsequent to ( as shown in fig3 b ) connection of the two parts . the reusable part ( 100 ) contains a peristaltic pumping mechanism provided with rotary wheel ( 110 ) and a driving mechanism ( 120 ) having a motor ( 121 ), a worm ( 126 ), a shaft ( 128 ) and gears ( 124 ). the reusable part ( 100 ) also contains electronic components ( 130 ). the disposable part ( 200 ) includes reservoir ( 220 ), delivery tube ( 230 ), power source ( 240 ), exit port ( 213 ), and stator ( 190 ). the power source ( 240 ) may be a zinc - air battery or button battery . fig4 a - b show embodiments of the dispensing unit ( 10 ) employing a piston - plunger pumping mechanism for dispensing fluid to a user &# 39 ; s body . fig4 a shows a two - part dispensing unit ( 10 ) having a reusable part ( 100 ) and a disposable part ( 200 ). the disposable part ( 200 ) includes reservoir ( 220 ) provided with plunger assembly ( 110 ), power source ( e . g ., battery ) ( 240 ), energy storage device ( 252 ), and exit port ( 213 ). in alternative embodiments , the plunger assembly ( 110 ) may be located in the reusable part ( 100 ) or be shared by both parts . the reusable part ( 100 ) includes a driving mechanism ( 120 ), which has a motor ( 121 ) ( e . g ., stepper motor , dc motor , or sma actuator ) and a driving gear ( not shown ) for displacing the plunger assembly ( 110 ). the driving mechanism ( 120 ) is controlled by electronic components ( 130 ), which has a controller ( not shown ), a processor ( 132 ), a transceiver ( 131 ), and / or a transmitter ( 133 ). infusion programming can be carried out by a remote control unit ( not shown ) and / or by one or more buttons ( 15 ) provided on the dispensing unit ( 10 ). the power source ( 240 ) may be located in the reusable part ( 100 ) and may be rechargeable . an example of such a dispensing unit is disclosed in the co - owned , co - pending u . s . provisional patent application no . 61 / 123 , 509 , filed on apr . 9 , 2008 , the disclosure of which is incorporated herein by reference in its entirety . fig4 b shows a single - part dispensing unit ( 10 ), which includes substantially similar components as the two - part dispensing unit ( 10 ). the components of the single - part dispensing unit ( 10 ) are deployed within a common housing ( 11 ). the embodiments shown in fig4 a - b are disclosed in the co - owned , co - pending international patent application no . pct / il2008 / 000641 , the disclosure of which is incorporated herein by reference in its entirety . any of the above - mentioned embodiments may be provided with a sensing and monitoring device for controlling operation of the driving mechanism ( 120 ). fig5 shows this device employing a photo interrupter ( 113 ) as disclosed in the co - owned , co - pending international patent application no . pct / il2008 / 000642 , the disclosure of which is incorporated herein by reference in its entirety . the sensing and monitoring device is provided with an encoder vane ( 116 ) configured as a 180 degree sector , which is affixed to a shaft ( 128 ) such that the encoder vane ( 116 ) rotates with the shaft ( 128 ) at the same rotational velocity . photo - interrupter ( 113 ) is positioned such that as encoder vane ( 116 ) rotates it passes through space ( s ) between led ( 112 ) and light detector ( 114 ). the motor &# 39 ; s ( 121 ) rotational velocity can be derived from the shaft &# 39 ; s ( 128 ) rotational velocity by taking into consideration the gear ( 124 ) reduction ratio . for example , when the shaft ( 128 ) rotates at 1 rotation per minute ( rpm ) and the gear ( 124 ) ratio is 3 : 1 ; the motor &# 39 ; s ( 121 ) speed is 3 rpm . other sensing and monitoring devices may also be employed to measure the motor &# 39 ; s ( 121 ) rotational velocity . fig6 shows schematically the power source ( 240 ) and energy consuming components of the dispensing unit ( 10 ) controlled by controller ( 132 ). the energy consuming components include : a communication device ( 134 ), which may include without limitation rf , ir and other communication types ( e . g ., magnetic relay , manual buttons , audible commands ). a pumping mechanism ( 136 ) actuated by a driving mechanism having a motor and motor driver . a sensing and monitoring device ( 138 ), which may include without limitation an occlusion sensor or motion sensor . an indication device ( 140 ), ( also referred to as “ notification device ”), which may include without limitation a buzzer or vibration alarm . fig7 shows a flow chart depicting an energy supply and control of the motor ( 121 ). in practice , a low price , small - sized power source ( 240 ) ( e . g ., button battery ) may be used , particularly a small quantity thereof , to provide a dispensing unit ( 10 ) that is of miniature size and lightweight . due to the small size of a button battery , the electrical power output produced thereby , i . e ., current (“ i ”) and voltage (“ v ”), is substantially lower than the electrical power required for motor operation , i . e ., a condition is satisfied whereby for example , a zinc - air battery has a maximum power output of about 0 . 03 watts ( e . g ., current of about 25 ma and voltage of about 1 . 2 volts ), while the motor ( 121 ) requires electrical power of 1 . 5 watts ( e . g ., current of about 500 ma and voltage of about 3 volts ). it can be seen in this example that the electrical power ( w motor ) required the motor is times larger than what battery ( w battery ) is able to supply . the electric power required by the motor is not limited to the particular electrical power indicated above . thus , in order to enable operation of the motor ( 121 ), the voltage and current supplied thereto are increased . voltage increase can be carried out by virtue of a dc - dc converter ( 254 ) which can for example convert the 1 . 2 volts supplied by the battery , i . e ., power source ( 240 ), to the voltage required by the motor ( 121 ), i . e ., 3 volts . increasing the current can be carried out by a pulsed power method , i . e ., by charging the energy storage device ( 252 ) ( e . g ., a 0 . 2 f capacitor ) for approximately 1 second and then discharging it for about 20 milliseconds . this enables multiplication of the current by 50 times . the 3v voltage is also supplied to the controller ( 132 ) and to the sensing and monitoring device ( 138 ) ( e . g ., revolution counters ). such a sensing and monitoring device ( 138 ) is disclosed in the co - owned , co - pending international patent application no . pct / il2008 / 000642 , as noted above . the motor driver ( 255 ), which is controlled by the controller ( 132 ), operates the motor ( 121 ) by providing it with a pulsed power , as shown by line ( 109 ). the pulsed power is supplied by the energy storage device ( 252 ). in some embodiments , the motor &# 39 ; s ( 121 ) operation is controlled by the principle of a closed - loop feedback , according to which the amount of power supplied to the motor ( 121 ) is adjusted based on the motor &# 39 ; s ( 121 ) rotational velocity ( 38 ). sensing and monitoring device ( 138 ) ( e . g ., revolution counter or rotation sensor ) measures the motor &# 39 ; s ( 121 ) output as shown by dashed line ( 22 ) and provides the controller ( 132 ) with the required data , including without limitation , the motor &# 39 ; s ( 121 ) instant rotational velocity , as shown by dashed line ( 38 ). in some embodiments , the sensing and monitoring device ( 138 ) merely provides a number of revolutions of the motor ( 121 ), while the velocity is calculated by the controller ( 132 ). in some embodiments , the motor &# 39 ; s ( 121 ) mechanical energy may be converted into electrical energy , as shown by line ( 108 ). this energy can be stored in the energy storage device ( 252 ) for later use . fig8 a - b show the main components depicted in fig7 : the motor ( 121 ), the energy storage device ( 252 ), and the power source ( 240 ) connected by flat strip connectors ( 241 ) to other electrical components ( 130 ). the energy storage device ( 252 ) can be a high capacity capacitor having a capacity of 180 mf to 200 mf . it is advantageous if the capacitor has a flat configuration and reduced dimensions ( e . g ., 29 mm × 17 mm × 0 . 9 mm ). consequently , the capacitor may be placed parallel to the electronic components ( 130 ) ( e . g ., a printed circuit board ), which allows the dispensing unit ( 10 ) to be kept as small and thin as possible . in practice , the capacitor having the above - mentioned configuration and dimensions provides a dispensing unit having thickness less than 15 mm . fig9 a - b are power - time plots illustrating a pulsed power produced by a capacitor and supplied to the motor . in some embodiments , the supply of pulsed power includes two modes : accumulation mode ( 400 ) and release mode ( 500 ). during the accumulation mode ( 400 ), a battery charges the capacitor . during the release mode ( 500 ), the capacitor is being discharged and supplies current to power consuming components of the dispensing unit , including without limitation , the motor and electronic elements . the ratio between the accumulation time t (“ t accumulaton ”) and release time (“ t release ”) “ t release ”) is proportional to the ratio between the power required for operation of power consuming components , such as a motor (“ w motor ”) and the electrical power outputted by a battery (“ w battery ”), i . e ., fig9 a shows a graph of a typical charging / discharging cycle of the capacitor having the two modes . it is clear that the duration of the accumulation mode ( 400 ) is substantially longer than the release mode ( 500 ). in practice , this duration may be 50 times longer . therefore , the maximal pulse train duration applied for activating the motor is less than the release mode ( 500 ) duration . in alternative embodiments , the charge stored in the capacitor may be monitored ( e . g ., by an a / d converter ), thereby allowing a dynamic control over the discharging and recharging of the capacitor to be achieved . fig9 b shows schematic graphs of the power (“ power ”) and current (“ i ”) of a charging / discharging cycle of the capacitor . during accumulation mode ( 400 ), the energy that is supplied by the battery is accumulated and stored in the capacitor . in practice , when applying a 0 . 2 f capacitor and a zinc - air battery , it may take 980 milliseconds . the energy ( p 1 ) that is stored in the capacitor gradually increases while the supplied current ( i 1 ) remains constant . during the release mode ( 500 ), the capacitor discharges and , supplies the required amount of power to the power consuming components . when the capacitor has 0 . 1 f capacity and the battery is a silver - oxide button - sized battery with 0 . 186 watt output , the release mode can take 10 milliseconds , while the accumulation time is about 8 times higher . discharged power and current are designated as p2 and i2 , respectively . in some embodiments , there may be continued charging of the capacitor , even during the discharge phase , which shortens the time interval between two consecutive pulses . if the capacitor is fully loaded , the charging process may not continue . fig1 a shows the angular velocity ( ω m ) of the motor versus time ( t ) and fig1 b shows the corresponding power ( p ) discharged from the capacitor and supplied to the motor . during this period , the motor operates the pump to deliver fluid ( e . g ., insulin ) via the dispensing unit . when the motor is rotated based on energy from the capacitor only a limited amount of fluid can be delivered during a single charging / discharging cycle and , therefore , more than one cycle may be required to deliver the appropriate amount of fluid required for therapeutic treatment . in some embodiments , a variant pulse train can be supplied to the motor each time the capacitor is being discharged . the amount of power supplied during the discharge of the capacitor depends upon whether the motor rotates with constant or variable rotational velocity . at t = t 0 , the motor begins to rotate and its rotational velocity should be gradually increased up to a certain velocity . the increasing velocity is designated as a 1 . the velocity increases due to supplying a certain amount of electrical power delivered by the capacitor to the motor ( p & gt ; 0 ). this power is designated as b 1 . at t = t 1 , the motor &# 39 ; s angular velocity is constant , as represented on the graph in fig1 a as a plateau . the achieved velocity is designated as a 2 . the amount of power required to keep the motor rotating at constant velocity a 2 can be b 2 , which is less than b1 since constant angular velocity ( ω m ) is maintained due to inertia . thus , the required power ( b 2 ) is less than b 1 . during the time interval from t = t 2 to t = t 3 , the velocity of the motor is decreased until full stop ( the decreasing velocity is designated as a 3 ). the velocity can be reduced by supplying power b3 , as may be required to overcome inertia until stopping the motor . in some embodiments , the time interval from t = t 1 to t = t 3 is about 20 milliseconds . the pattern of the pulses is typically predetermined when the pulse trains are tailored . that is , the dispensing pump is initially configured with at least one pulse train . in some embodiments , the dispensing pump controller can adjust and combine various pulses and pulse trains as needed . in other embodiments , the controller can adjust and schedule the pulse train ( e . g ., energy , number of pulses , width of pulses , or frequency ) based on the energy stored in the energy storage device or power source . fig1 a - b refer to another embodiment and show graphs of the angular velocity ( ω m ) of the motor versus time ( t ) and the corresponding power ( p ) required by the motor versus time ( t ). the graphs depict variations in velocity and power during drug delivery , while an alternative operational mode of the motor is employed for saving energy . the two first phases designated by a 1 , a 2 and b 1 , b 2 are identical to those referred to in fig1 a - b . during the time interval starting at t = t 2 and ending at t = t 3 , the velocity of the motor is decreased merely due to friction forces until a full stop ( the reducing velocity is designated in fig1 a as a 4 ). fig1 b shows that in this time interval ( t = t 2 to t = t 3 ), the motor continues to rotate and no energy is required . therefore , energy associated with the rotation of the motor is available for use by the energy consuming components while the motor itself does not require supply of energy , i . e ., during this phase the motor may operate like a dynamo . fig1 shows current ( i ) supplied to the motor versus time ( t ), during a pulse train employing the operation mode described in fig1 a - b . the current ( i ) is supplied by pulses while each pulse is characterized by a time interval (“ t ”) ( i . e ., a period ). the initial pulse ( e . g ., between t 1 and t 2 ) has long period t 1 , typically lasting for 1 to 1 . 5 millisecond , for setting the driving mechanism into motion and for accelerating the motor . the duration of each consecutive pulse is either equal or shorter than the former . in some embodiments , the second phase has a minimal pulse period t 2 of about 0 . 5 milliseconds . this trend is turned over when the motor speed is decreased , i . e ., in this phase the motor is decelerating and each period t 3 of each pulse is either equal or longer than the former . for example , the duration of the n pulses of an exemplary pulse train can be written as shown in the following equation : since a pulse duration ( t ) is inversely proportional to the angular velocity of the motor ( ω ), ( t α 1 / ω ), the above equation can be accordingly rewritten as follows : according to some embodiments , every pulse is tailored to rotate the motor &# 39 ; s axis through an identical angle ( known as a ‘ step ’). enabling a constant angular rotation resulting from each discrete pulse and providing the same amount of fluid is highly advantageous in that it simplifies the dispensing pump control and calibration , for example , when calculating the number of pulses needed to deliver a required amount of therapeutic fluid . this is achieved by maintaining constant the multiple of pulse duration by the rotational velocity it causes : t 1 · ω 1 = t 2 · ω 2 = t 3 · ω 3 = . . . t n − 1 · ω n − 1 = t n · ω n = 18 ° fig1 - 14 shows current ( i ) supplied to the motor versus time ( t ), according to some embodiments . conventional methods for supplying energy to motors of infusion devices employ pulses in which a constant level of power is provided to the motor during each pulse period ( i . e ., a 100 % duty cycle ). this method can be employed to the device disclosed herein as well , i . e ., power pulse trains may be supplied to the motor while each pulse train includes pulses of power during which power would be supplied non - invariantly at three various levels b 1 , b 2 and b 3 lasting during respective periods t 1 , t 2 and t 3 following without interruption . in some embodiments , supply of power may be organized during each pulse with interruptions . as shown schematically in fig1 there could be provided three different operational phases and each pulse of the pulse train includes : a discharge phase ( 510 )— pulsed power is provided to the motor by discharging a capacitor . a null phase ( 520 )— power supply is interrupted and power is not supplied to and neither generated by the motor . a charge phase ( 530 )— energy is generated by the motor and this energy can be supplied to power consuming components . the pulses typically include discharge ( 510 ) and null ( 520 ) phases or null ( 520 ) and charge ( 530 ) phases but may include only discharge ( 510 ) or charge ( 530 ) phases . fig1 shows a graph of the current ( i ) supplied to the motor versus time ( t ), for generating the angular velocity according to principles described in connection with fig1 a - b . the graph shows a single pulse train , which includes three initial pulses . each one of initial pulses ( e . g ., the pulses designated as p 1 , p 2 and p 3 ) have two phases : a discharge phase ( 510 ) ( designated as w 1 , w 2 and w 3 ), followed by a null phase ( 520 ). in some embodiments , the null phase ( 520 ) is 10 % to 30 % of the pulse period , i . e ., the width of these pulses is of 70 % to 90 %. in some embodiments , the dispensing pump controller applies pulse width modulation ( pwm ) for changing the width of the pulses to generate the determined pulse train . it should be appreciated that other methods for exploiting the motor &# 39 ; s inertia for reducing the energy supply may be implemented , such as by changing the pulse period , amplitude , or shape ( e . g ., triangle , square , sine wave ). halting motor operation is carried out by the last pulses of the pulse train ( e . g ., p n − 1 and p n ). the discharge phase ( 510 ) of these pulses equals the duty cycle ; p n − 1 = ω n − 1 and p n = ω n . this causes the motor to stop almost immediately , so that no excess fluid is delivered by the dispensing unit . fig1 shows a graph of current ( i ) supplied to the motor versus time ( t ), for implementing the principle described above in connection with fig1 a - b . the graph shows a pulse train . the last pulses of the pulse train ( e . g ., p n − 1 and p n ) include a single phase , i . e ., the charge phase ( 530 ). this mode of operation enables the motor to generate energy due to its rotation and to transfer it to an energy storage device . the halting method is shown in fig1 a - b and may require the use of a sensing and monitoring device ( e . g ., a sensor ) to detect the relative position ( i . e ., angle ) of the rotary wheel . the sensing and monitoring device may be required to achieve an accurate fluid delivery employing a flow correction mechanism . although particular embodiments have been disclosed herein in detail , this has been done by way of example for purposes of illustration only , and is not intended to be limiting with respect to the scope of the claims . in particular , it is contemplated by the inventors that various substitutions , alterations , and modifications may be made without departing from the spirit and scope of the devices and methods defined by the claims . other aspects , advantages , and modifications are considered to be within the scope of the claims . the claims presented are representative of the devices and methods disclosed herein . other , presently unclaimed devices and methods , are also contemplated . the inventors reserve the right to pursue such devices and methods in later claims . the following examples serve to illustrate embodiments of the disclosed devices and methods and are given for illustrative purposes only and are not intended to limit the present disclosure . fig1 , 16 and 17 show examples of pulse train supplied to the motor according to some embodiments . these figures show the discharge phase ( 510 ), in which power is supplied to the motor , the null phase ( 520 ) in which no power is supplied to the motor and the charge phase ( 530 ) when power is generated by the motor . the pulse trains were tailored to reduce the power provided to the motor while each pulse rotates the motor by 20 degrees . the power source in these examples is a zinc - air button battery , a 0 . 2 f capacitor and two phase motor commercially provided by nidec copal corporation ( u . s . a .). the pulses are provided by pwm and / or by changing the pulse period . fig1 shows a pulse train for rotating the motor by 160 degrees composed of three sets of pulses : the first set of pulses is applied for accelerating the motor and includes three pulses lasting for 2 . 3 milliseconds . the second set of pulses is designed for maintaining the motor speed and includes four pulses , each having a 1 . 15 millisecond period . this set of pulses rotates the motor by the same angle as the first set but requires 50 % less power . to increase the energy efficiency , the last two pulses may have 80 % width of the duty cycle . the third set of pulses is for stopping the motor and is identical to the first set but in reversed phase . in this example all the pulses have 100 % pulse width ( i . e ., the pulse width equals the pulse duration ). fig1 shows a pulse train designed to rotate the motor by 520 degrees at a lower rotation velocity than that disclosed in example 1 . this pulse train is composed of three sets of pulses : the first set of pulses is applied for accelerating the motor and includes four pulses lasting for 1 . 0 millisecond . the second set of pulses is designed for maintaining the motor speed and includes 22 pulses , each having a 0 . 7 millisecond period . if the pulses in this set were tailored as the first set ( as described in the prior art ), the energy consumption of this set would be 40 % higher . the third set of pulses includes two stop pulses lasting for 1 . 0 millisecond , wherein a 90 % duty cycle is applied to stop the motor rotation . fig1 shows a pulse train that does not apply power to stop the motor . the pulse train includes two sets of pulses : the first set of pulses is applied for accelerating the motor and includes four pulses lasting for 1 . 0 millisecond . the second set of pulses is designed for maintaining the motor speed and includes 22 pulses , each having a 0 . 7 millisecond period . also shown are two pulses ( 530 ) supplied by the motor for recharging the capacitor , i . e ., the motor functions as a dynamo by transferring kinetic energy to electrical power . example 3 requires less energy than the pulse train described in example 2 and provides two more steps to the motor ( which are applied to stop the motor in example 2 ). the inertia of the motor at the end of this pulse train can be converted by the motor to electrical power , which can be provided to other electrical components of the dispensing unit . this pulse train requires 29 . 1 j , provides 26 steps of rotation and can also retrieve part of the excess power provided to the motor . a standard method of motor activation would be composed of 20 pulses lasting 1 . 0 millisecond each , whereby at least two of them are applied for stopping the motor . thus , less than 20 steps can be provided in this method .
devices and methods for powering a medical device for sustained delivery of fluids or continuous monitoring of body analyte are disclosed . the devices may comprise a pumping mechanism , a driving mechanism for activating the pumping mechanism to dispense fluid , and a power source coupled to the driving mechanism and having an energy storage cell for providing a pulsed power to the driving mechanism . the methods may be implemented by activating the driving mechanism using pulsed energy in the form of at least one pulse train pattern accumulated in and discharged from an energy storage component .