in the following detailed description , reference is made to the accompanying drawings which form a part hereof , and in which is shown by way of illustration specific embodiments in which the present invention may be practiced . these embodiments , which are also referred to herein as “ examples ,” are described in sufficient detail to enable those skilled in the art to practice the invention , and it is to be understood that the embodiments may be combined , or that other embodiments may be utilized and that structural , logical and electrical changes may be made without departing from the scope of the various embodiments of the present invention . the following detailed description is , therefore , not to be taken in a limiting sense , and the scope of the present invention is defined by the appended claims and their equivalents . in this document , the terms “ a ” or “ an ” are used , to include one or more than one . in this document , the term “ or ” is used to refer to a nonexclusive or , unless otherwise indicated . in addition , as used herein , the phrase “ pixel ” also includes embodiments of the present invention where the data is represented by a “ voxel ”. thus , both the terms “ pixel ” and “ voxel ” may be used interchangeably throughout this document . also as used herein , the phrase “ reconstructing an image ” is not intended to exclude embodiments of the present invention in which data representing an image is generated , but a viewable image is not . therefore , as used herein , the term “ image ” broadly refers to both viewable images and data representing a viewable image . however , many embodiments generate ( or are configured to generate ) at least one viewable image . various embodiments may be implemented in connection with different types of imaging systems . for example , various embodiments may be implemented in connection with a ct imaging system in which an x - ray source projects a fan - shaped beam that is collimated to lie within an x - y plane of a cartesian coordinate system and generally referred to as an “ imaging plane .” the x - ray beam passes through an object being imaged , such as a patient or baggage . the beam , after being attenuated by the object , impinges upon an array of radiation detectors . the intensity of the attenuated radiation beam received at the detector array is dependent upon the attenuation of an x - ray beam by the object . each detector element of the array produces a separate electrical signal that is a measurement of the beam intensity at the detector location . the intensity measurement from all the detectors is acquired separately to produce a transmission profile . in third generation ct systems , the x - ray source and the detector array are rotated with a gantry within the imaging plane and around the object to be imaged such that the angle at which the x - ray beam intersects the object constantly changes . a complete gantry rotation occurs when the gantry concludes one full 360 degree revolution . in an axial scan , the projection data is processed to construct an image that corresponds to a two - dimensional slice taken through the object . one method for reconstructing an image from a set of projection data is referred to in the art as a filtered backprojection technique . this process converts the attenuation measurements from a scan into integers called “ ct numbers ” or “ hounsfield units ” ( hu ), which are used to control the brightness of a corresponding pixel on a cathode ray tube display . to reduce the total scan time , a “ helical ” scan may be performed . to perform a “ helical ” scan , the patient or the baggage is moved while the data for a prescribed number of slices is acquired . such a system generates a single helix from a fan beam helical scan . the helix mapped out by the fan beam yields projection data from which images in each prescribed slice may be reconstructed . reconstruction algorithms for helical scanning typically use helical weighting algorithms that weight the acquired data as a function of view angle and detector channel index . specifically , prior to a filtered backprojection process , the data is weighted according to a helical weighing factor , which is a function of both the gantry angle and the detector angle . the weighted data is then processed to generate ct numbers and to construct an image that corresponds to a two - dimensional slice taken through the object . referring to fig1 and 2 , a computed tomography ( ct ) imaging system 10 is shown that includes a gantry 12 for a ct scanner . gantry 12 has a radiation source such as an x - ray source 14 that projects a beam of radiation such as x - rays 16 toward a detector array 18 on the opposite side of gantry 12 . detector array 18 is formed by a plurality of detector rows ( not shown ) including a plurality of detector elements 20 that together sense the projected x - rays that pass through an object 22 , for example a medical patient or a piece of luggage , between array 18 and source 14 . detector array 18 may be fabricated in a single slice or multi - slice configuration . each detector element 20 produces an electrical signal that represents the intensity of an impinging radiation ( e . g ., x - ray ) beam and hence can be used to estimate the attenuation of the beam as the beam passes through object or patient 22 . during a scan to acquire x - ray projection data , gantry 12 and the components mounted thereon rotate about a center of rotation 24 . fig2 shows only a single row of detector elements 20 ( e . g ., a detector row ). however , multi - slice detector array 18 may include a plurality of parallel detector rows of detector elements 20 such that projection data corresponding to a plurality of quasi - parallel or parallel slices can be acquired simultaneously during a scan . rotation of components on gantry 12 and the operation of x - ray source 14 are governed by a control mechanism 26 of ct system 10 . control mechanism 26 includes an x - ray controller 28 that provides power and timing signals to x - ray source 14 and a gantry motor controller 30 that controls the rotational speed and position of gantry 12 . a data acquisition system ( das ) 32 , in control mechanism 26 , samples analog data from detector elements 20 and converts the data to digital signals using an encoder 21 for subsequent processing , and a trigger 21 that receives an encoder signal 23 from the encoder 21 . the trigger 21 produces a projection acquisition signal 27 that commands the das 32 to sample the detected image data from the detector . in one embodiment the trigger 21 may include a digital phase locked loop that may be configured to rapidly change a triggering output signal based on a rapid change in gantry rotational speed , ( e . g ., speed change between heartbeats ), where the output signal has minimal jitter . the das 32 outputs projection data sets including attenuation measurements obtained at particular gantry rotation angles ( e . g ., view angles ). as the gantry 12 rotates a plurality of views may be acquired during a single rotation . a single rotation being one complete 360 degree revolution of the gantry 12 . each view has a corresponding view angle and thus , a particular location on the gantry 12 . for instance , for each gantry rotation , there may be 1 , 000 views , where a view angle is 0 . 36 degrees . the projection data sets correspond to a particular view angle as the gantry 12 rotates about a patient 22 . a group of projection data sets form a complete scan of the patient 22 . for instance , a complete scan of a region of interest of the patient 22 may include a complete set of projection data sets ( e . g ., multiple projection data sets corresponding to multiple views during a single complete rotation of gantry 12 ). an image reconstructor 34 receives sampled and digitized x - ray data from das 32 and performs high - speed image reconstruction . the reconstructor 34 may produce data sets that represent volumetric data sets or image slices through patient 22 . the reconstructed image is output by the image reconstructor 34 and applied as an input to a computer 36 , which stores the image in a storage device 38 ( e . g ., memory ). the image reconstructor 34 can be specialized hardware or computer programs executing on computer 36 . computer 36 also receives commands and scanning parameters from an operator via console 40 that has a keyboard or other suitable input device . an associated cathode ray tube display 42 or other suitable display device allows the operator to observe the reconstructed image and other data from computer 36 . the operator supplied commands and parameters are used by computer 36 to provide control signals and information to das 32 , x - ray controller 28 , and gantry motor controller 30 . in addition , computer 36 operates a table motor controller 44 , which controls a motorized table 46 to position patient 22 in gantry 12 . particularly , table 46 moves portions of patient 22 through gantry opening 48 . in one embodiment , computer 36 includes a device 50 , for example , a floppy disk drive , cd - rom drive , dvd drive , magnetic optical disk ( mod ) device , or any other digital device including a network connecting device such as an ethernet device for reading instructions and / or data from a computer - readable medium 52 , such as a floppy disk , a cd - rom , a dvd or another digital source such as a network or the internet , as well as yet to be developed digital means . in another embodiment , computer 36 executes instructions stored in firmware ( not shown ). in some configurations , computer 36 and / or image reconstructor 34 is / are programmed to perform functions described herein . also , as used herein , the term computer is not limited to just those integrated circuits referred to in the art as computers , but broadly refers to computers , processors , microcontrollers , microcomputers , programmable logic controllers , application specific integrated circuits , and other programmable circuits , and these terms are used interchangeably herein . although the specific embodiment mentioned above refers to a third generation ct system , the methods described herein equally apply to fourth generation ct systems ( e . g ., a stationary detector with a rotating x - ray source ) and fifth generation ct systems ( e . g ., a stationary detector and an x - ray source ). additionally , it is contemplated that the benefits of the invention accrue to imaging modalities other than ct , for example , mri , spect , and pet as well as ct baggage scanners . thus , each projection data set is associated with a particular table position and gantry rotation angle at which the projection data set was acquired . each corresponding projection data set is stored in memory 38 . the memory 38 stores a group of projection data sets for a complete scan or examination of patient 22 , a group of projection data sets that correspond to a volumetric area of the patient 22 , as well as projection data sets used to update an image . fig3 illustrates a block diagram of a digital trigger interpolation system 60 constructed in accordance with an embodiment of the present invention . system 60 includes a prescale module 62 , a digital phase locked loop 64 , a remainder module 66 , and a trigger interpolation module 68 . the prescale module 62 receives , as input from the encoder 25 ( shown in fig2 ), a series of pulses 70 . the prescale module 62 samples the input pulses 70 , to create a scaled pulse train . the frequency of the scaled pulse train may be selected by a q - set value 72 , which either multiplies or divides the initial encoder pulse train 70 . for instance , to perform multiplication by using a high - speed system clock source and a digital divider , as described below . the output of the prescale module 62 is a scaled pulse train 74 , which is input into the digital phase locked loop 64 ( dpll ). the dpll 64 further receives a preset signal 76 and a p - div signal 78 as inputs . the preset signal 76 is generated by a processor external to the dpll 78 and may be used to seed a change in trigger output frequency as the result of a change in the speed of a motor ( not shown ) by setting a desired accumulator value . the p_div signal 78 may be used to set a value to divide the output feedback of the dpll 64 , as described in detail below . the dpll 64 responds to changing input frequencies to produce a stable output signal 80 having minimal jitter . the output of the dpll 64 may be an arbitrary number of pulses based on a pre - determined number of input pulses from the encoder 70 . optionally , the output 80 of the dpll 64 may be input to a remainder - fix module 66 . the remainder - fix module 66 receives an “ int ” signal 82 , a “ rem ” signal 84 , and an “ out set ” signal 86 . the int signal 82 may set the number of counts that correspond to an integer portion of a division operation ( e . g ., integer ( input pulses / rotation )( output pulses / rotation )), as described in detail below . the rem signal 84 may set the number of counts which correspond to the portion of a remainder operation ( e . g ., rem ( input pulses / rotation )/( output pulses / rotation )). the out set signal 88 may set the desired number of rotations per second . furthermore , the output of the remainder - fix module 66 may be input to a trigger interpolator module 68 , which is described in detail below . fig4 illustrates a flow diagram of a series of steps for a process 400 performed in accordance with an embodiment of the present invention . the process 400 may be implemented by one or more devices and apparatus discussed above in connection with fig1 - 3 . at 402 , the process commences by initiating the medical apparatus to cause the gantry 12 to start revolving around a patient 22 . at 404 as the gantry 12 rotates , an encoder 25 ( shown in fig2 ) generates an encoder signal 23 corresponding to projection triggers to be produced by trigger module 21 for each projection . the encoder signal 23 may be a plurality of pulses . the pulses may be equally spaced having the same interval between each pulse . alternatively , the pulses may be separated by intervals having varying length of times due to mechanically or electrically induced jitter or change in system speed . at 406 , the encoder signal 23 may be input to the pre - scaler module 62 . fig5 illustrates a module diagram 100 of the pre - scaler module 62 used in accordance with an embodiment of the invention . the pre - scaler module 62 includes a divide factor component 102 , a multiply factor component 104 , a feedback element 106 , and a compare component 108 . the divide factor 102 implements a transfer function . in one embodiment , the transfer function is determined by the following equation : where “ input signal ” is the scaled encoder input , “ pre - scale set 1 ” is a user selected factor used to divide the scaled encoder input , and “ pre - scale set 2 ” is a user selected value to lower the system clock frequency ( e . g ., shown as hf clk 103 ) in order to perform the multiply . the division portion of the transfer function ( e . g ., ( input signal / pre - scale set 1 )) may be performed the divide factor 102 , for example , implemented as a counter . the divide factor 102 may divide the encoder signal 23 based on a user selected value , ( e . g ., a factor of two , five , ten , one - hundred , and the like ). the multiplication portion of the transfer function may be performed in real - time and implemented by the compare component 108 . the compare component 108 compares a count from the divided pulse train 107 with a count 109 from the feedback element 106 . a pulse is generated when the count 109 is equal to the count 107 from the divided pulse train . the generated pulse effectively multiplies the divided pulse train 107 by the pre - scale set 2 value . multiplying by the pre - scale set 2 value may not be utilized , and may be used when necessary to attain a specific target frequency . returning to fig4 , at 408 , the scaled pulse train 110 is input to the dpll 64 ( shown in fig3 ). fig6 illustrates a detailed block diagram 120 of the dpll 64 constructed in accordance with an embodiment of the invention . the dpll 64 may be configured as a field programmable gate array ( fpga ), an application specific integrated circuit ( asic ), constructed from discrete logic , and the like . as shown in fig6 , the dpll 64 includes a phase / frequency ( phase / freq ) component 122 , a controller 124 , a multiplexer ( reg / mux ) 126 , a digital controlled oscillator ( dco ) 128 and a register 130 ( e . g ., reg ). the phase / freq component 122 accepts the following as input : the scaled pulse train 110 and a value 111 ( e . g ., p_div ) to divide the output of pll represented as a feedback signal 132 from bus b 133 . the phase / freq component 122 may be a phase detector that detects differences in phase between the input signal 110 and the output signal 132 . alternatively , the phase / freq component 122 may be a state machine that determines which of the two signals 110 , 132 has a zero - crossing earlier or more often . for example , the phase / freq component 122 compares the output signal 132 with the inputs signal 110 to determine a correction between the output signal 132 and the input signal 110 . for instance , compared to the output signal 132 , the input signal 110 may lag , lead , be too fast , or be too slow . a correction may be provided by the phase / frequency component 122 . for instance , an error correction signal 116 ( e . g ., corr_err ) may be generated along with a signal indicating how to correct for a lag 112 , a lead 113 , a fast signal 114 , or a slow signal 115 . the error correction signal 116 ( e . g ., corr_err ) along with the lag 112 , lead 113 , fast 114 , and slow 115 signal may be used by the controller 124 to add or subtract a value from the dco 128 . the correction error signal 116 may indicate an amount of correction required to increase convergence speed to a desired output signal . returning to fig4 , at 410 , the changed output signal value 132 may command the data acquisition system to capture at a new frequency corresponding to change in gantry speed . at 412 , the dpll 120 output signal 132 may be corrected by selecting a linear correction method . for instance , the controller 124 ( shown in fig6 ) may accept a current value 117 from the dco 128 ( e . g ., an accumulator ) that maybe fed back from the output signal 132 . the current value 117 together with the error correction signal ( e . g ., lag 112 , lead 113 , fast 114 , slow 115 , and the like ) provided by the phase / freq module 122 , a new accumulator value may be generated ( e . g ., k_out 125 ). alternatively , the correction error may be a non - linear correction that may be used to “ inject a seed value ” to rapidly lock the output signal 132 to a desired value . for example , the controller 124 may accept a dynamic enable signal 123 ( dyn_en ) having a “ high value ” ( e . g ., a one ) to accept a seed value . when the dynamic enable signal 123 changes states from a zero to a one , a non - linear correction mode may be selected ( e . g ., corr_err 116 value is set to a correction amount ), and the signal 116 latches into controller 124 the correction value . the corr_err value is “ injected ” as the seed value into controller 123 to force the output signal 132 to rapidly approach the desired value . thus , when dynamically latching a correction value using the non - linear operation mode , the seed value may be output from controller 124 on signal line ffw_out 119 . optionally , the correction value may be output on the k_out 125 signal line if the multiplexer 126 is implemented in the controller block . the multiplexer 126 may accept the new accumulator value , k_out 125 . the multiplexer 126 may select a value to linearly correct the output signal 132 . alternatively , the multiplexer 126 may select a correction value ( e . g ., a non - linear convergence mode ), when a seed value is used , to narrow the difference of the output signal to a desired output signal value . the multiplexer control line ( mux_ctrl ) 129 selects which correction value to use , for example , the seed value on the ffw_out 119 signal line or the linear correction on the k_out 125 signal line . alternatively , when a new value for the output signal 132 is desired ( e . g ., after a change in rotational speed ), the mux_ctrl line 129 selects the preset_out line 131 , which may change the output signal 132 to lock to a new trigger frequency for accurate projection collection triggers at the new speed . a change in the dco 129 accumulator value may be implemented by the values of the k_out 125 signal line . for instance , the value of the k_out 125 signal line may be added to the dco 128 accumulator value . alternatively , the value of k_out 125 signal line may be subtracted from the dco 129 accumulator value . the selected value 127 may be input to the dco 128 along with a feedback signal 118 . for instance , the alu_ctrl line 133 may instruct the dco 128 to add or subtract data from the selected value 127 signal line from the feedback signal 118 , which may result in changing the speed of the output signal 132 . the dco 128 outputs a digital signal that may be wide enough to provide sufficient correction resolution to the register 130 . the dco 128 functions as an accumulator , and adjusts the output signal 132 by adding or subtracting an adjustment ( controlled by the alu_ctrl line 133 ). when the dco 128 overflows , a most - significant bit ( msb ) changes states ( e . g ., from a zero to a one ). the value of the msb may be output 134 . returning to fig4 , at 412 , when the output signal value 132 equals a desired value , no more adjustments are necessary . therefore , at 414 , the dpll 120 is locked at the desired value . at 416 , a remainder may be determined that may be accumulated and then added to a pulse . fig7 illustrates a block diagram 150 of the remainder - fix module 66 shown in fig3 utilized in accordance with an embodiment of the present invention . the remainder - fix module 66 enables an arbitrary number of encoder pulses 160 to generate output triggers 166 . the remainder - fix module 66 includes a remainder counter 152 , an integer counter 154 , a compare a element 156 and a compare b element 158 . the remainder - fix module 66 accepts pulses from the dpll 64 on the input line 160 . the remainder - fix module 66 implements a function : ( number of pll pulses per revolution / desired number of output pulses per revolution ). further , the remainder - fix module 66 accepts values for rem 165 , out_set 162 , and int 163 , for example , from a processor external to the imaging system 10 . the rem 165 may represent a numerator of a non - integer remainder of the transfer function , out_set 162 may represent a denominator of a non - integer remainder of the transfer function , and int may represent an integer portion of the transfer function . an exemplary example of the remainder - fix module 66 is described below . for instance , the pll may input 10 , 000 pulse per rotation , a desired number of output pulses may be set to 984 / rotation , the rem 165 may be set to 20 , out_set 162 may be set to 123 , and int 163 may be set to 10 . the remainder counter 152 may use the value of rem 165 to increment a “ rem_count .” the integer counter 154 may be incremented by a value of one for each input pulse entered on input 160 . after the first six input pulses , the integer counter 154 has a value of 6 ( e . g ., int_count = 6 ), and the remainder counter 152 has a value of 120 ( e . g ., rem_count = 6 * 20 = 120 ). on the seventh input pulse , the rem_count ( e . g ., rem_count = 7 * 20 = 140 ) is greater than the value of out_set 162 ( e . g ., 140 & gt ; 132 ). when the rem_count value exceeds the out_set 162 value , the value of rem_count may be adjusted according to : rem_count = rem_count − out_set ( e . g ., rem_count = 17 ). in addition , the hold signal 164 may be asserted to stop the integer counter 154 from incrementing ( e . g ., int_count remains at the last value , for instance , int_count = 6 ). thus , while the hold signal 164 is asserted , the integer counter 154 is prevented from incrementing . the arrival of the next pulse may de - assert the hold signal 164 . for each of the following input pulses 160 , both the integer counter 154 and the remainder counter 152 are incremented . for instance , on the eighth pulse , the integer counter 154 is incremented by a value of one , such that int_count = 7 , and the remainder counter 152 ( e . g ., rem_count = 17 ) is incremented by the value of rem 165 ( e . g ., 20 ), such that rem_count = 37 . when the value of int_count equals the value of int 163 ( e . g ., 10 ), an output pulse 166 is generated and the value of the integer counter is cleared ( e . g ., int_count = 0 ). for example , on the 11 th input pulse , int_count = 0 and rem_count = 97 . on the 13 th input pulse , rem_count ( e . g ., value of 137 ) has a value greater than out_set 162 ( e . g ., 123 ), which causes the hold signal 164 to be asserted and the value of rem_count to be adjusted ( e . g ., rem_count = rem_count − out_set = 137 - 123 = 15 ). the process repeats until output 166 has provided 984 pulses . returning to fig4 , at 418 , the value of the remainder may be spread over a plurality of encoder pulses . for example , in fig7 , the hold signal 164 may be used to determine when a predetermined amount of a remainder value has accumulated to add to a pulse . thus , by using the remainder - fix module 150 , an arbitrary number of encodes pulses may generate triggers for an arbitrary number of images to be acquired per gantry rotation with each image evenly spaced from each other . for example , the output 166 may have a value for a number of desired pulses per gantry rotation for an arbitrary input 160 pulse count . optionally , a trigger interpolator may be utilized to reduce scan failure from failed inputs to the dpll 120 ( shown in fig6 ). returning to fig4 , at 420 a trigger pulse may be injected in real - time when an input to the dpll 120 fails . the failure may be the result of noise , a communication error , an intermittent error , an instantaneous error , and the like . fig8 illustrates a block diagram of a trigger interpolator 180 ( shown in fig3 ) utilized in accordance with an embodiment of the present invention . the trigger interpolator 180 includes a delay window 182 and a pulse stuffer 184 . a pulse train 186 is input to the delay window , where the pulse train 186 may include a failure , such as a missed pulse . a trigger window 188 provides a value for a window for an expected pulse . a one shot trigger is generated on an interpolate signal 190 and input to the pulse stuffer 184 . a one - shot window 192 provides an ignore time period from register 130 ( shown in fig6 ). the ignore time allows a period of time for a signal to be held to avoid a double trigger . the interpolated signal 194 may be provided at a desired frequency value . the trigger interpolator 180 may be implemented in software . alternatively , the trigger interpolator 180 may be implemented in hardware . a technical effect of the various embodiments is to use a diagnostic or baggage imaging system , such as a computed tomography ( ct ) imaging system having a digital phase locked loop for multiplying and filtering encoder generated data acquisition signal ( das ) triggers to provide a predetermined number of pulses per gantry rotation . the digital phase locked loop may be injected with a desired frequency to quickly generate a desired output signal with minimal jitter . the various embodiments or components thereof may be implemented as part of a computer system . the computer system may include a computer , an input device , a display unit , and an interface , for example , for accessing the internet . the microprocessor may be connected to a communication bus . the computer may also include a memory . the memory may include random access memory ( ram ) and read only memory ( rom ). the computer system further may include a storage device , which may be a hard disk drive or a removable storage drive such as a floppy disk drive , optical disk drive , and the like . the storage device can also be other similar means for loading computer programs or other instructions into the computer system . in various embodiments of the invention , the method of creating a ct attenuation correction image as described herein or any of its components may be embodied in the form of a processing machine . typical examples of a processing machine include a general - purpose computer , a programmed microprocessor , a digital signal processor ( dsp ), a micro - controller , a peripheral integrated circuit element , and other devices or arrangements of devices , which are capable of implementing the steps that constitute the methods described herein . as used herein , the term “ computer ” may include any processor - based or microprocessor - based system including systems using microcontrollers , reduced instruction set circuits ( risc ), application specific integrated circuits ( asics ), logic circuits , and any other circuit or processor capable of executing the functions described herein . the above examples are exemplary only , and are thus not intended to limit in any way the definition and / or meaning of the term “ computer ”. the processing machine executes a set of instructions ( e . g ., corresponding to the method steps described herein ) that are stored in one or more storage elements ( also referred to as computer usable medium ). the storage element may be in the form of a database or a physical memory element present in the processing machine . the storage elements may also hold data or other information as desired or needed . the physical memory can be , for example , but not limited to , an electronic , magnetic , optical , electromagnetic , infrared , or semiconductor system , apparatus , device , or propagation medium . more specific examples of the physical memory include , but are not limited to , the following : a random access memory ( ram ) a read - only memory ( rom ), an erasable programmable read - only memory ( eprom or flash memory ), a hard disc drive ( hdd ) and a compact disc read - only memory ( cdrom ). the above memory types are exemplary only , and are thus limiting as to the types of memory usable for storage of a computer program . the set of instructions may include various commands that instruct the processing machine to perform specific operations such as the processes of the various embodiments of the invention . the set of instructions may be in the form of a software program . the software may be in various forms such as system software or application software . further , the software may be in the form of a collection of separate programs , a program module within a larger program or a portion of a program module . the software also may include modular programming in the form of object - oriented programming . the processing of input data by the processing machine may be in response to user commands , or in response to results of previous processing , or in response to a request made by another processing machine . in various embodiments of the invention , the method of creating can be implemented in software , hardware , or a combination thereof . the methods provided by various embodiments of the present invention , for example , can be implemented in software by using standard programming languages such as , for example , c , c ++, java , and the like . as used herein , the terms “ software ” and “ firmware ” are interchangeable , and include any computer program stored in memory for execution by a computer . it is to be understood that the above description is intended to be illustrative , and not restrictive . for example , the above - described embodiments ( and / or aspects thereof ) may be used in combination with each other . in addition , many modifications may be made to adapt a particular situation or material to the teachings of the invention without departing from its scope . while the dimensions , types of materials and coatings described herein are intended to define the parameters of the invention , they are by no means limiting and are exemplary embodiments . many other embodiments will be apparent to those of skill in the art upon reviewing the above description . the scope of the invention should , therefore , be determined with reference to the appended claims , along with the full scope of equivalents to which such claims are entitled . in the appended claims , the terms “ including ” and “ in which ” are used as the plain - english equivalents of the respective terms “ comprising ” and “ wherein .” moreover , in the following claims , the terms “ first ,” “ second ,” and “ third ,” etc . are used merely as labels , and are not intended to impose numerical requirements on their objects . further , the limitations of the following claims are not written in means - plus - function format and are not intended to be interpreted based on 35 u . s . c . § 112 , sixth paragraph , unless and until such claim limitations expressly use the phrase “ means for ” followed by a statement of function void of further structure .
a method and apparatus are provided for minimizing output pulse jitters in a phase locked loop . the method includes pre - setting the digital phase locked loop to a desired frequency , locking the digital phase locked loop to the desired frequency to generate an output signal , and filtering the output signal of the digital phase locked loop to maintain undesirable jitter to an acceptable range . in one embodiment , the apparatus is a medical imaging device . in another embodiment , the apparatus is a baggage imaging device .