the functions described as being performed at various components can be performed at other components , and the various components can be combined and / or separated . other modifications can also be made . all numeric values are herein assumed to be modified by the term “ about ,” whether or not explicitly indicated . the term “ about ” generally refers to a range of numbers that one of skill in the art would consider equivalent to the recited value ( i . e ., having the same function or result ). in many instances , the term “ about ” may include numbers that are rounded to the nearest significant figure . numerical ranges include all values within the range . for example , a range of from 1 to 10 supports , discloses , and includes the range of from 5 to 9 . similarly , a range of at least 10 supports , discloses , and includes the range of at least 15 . thus , the following disclosure describes data processing systems , methods , and apparatus for multi - modality imaging , including a system , a method , and an apparatus for optimizing the signal to noise ratio from an apd based detector in the presence of the time - varying electromagnetic field originating from the mri modality . many other examples and other characteristics will become apparent from the following description . one embodiment relates to a signal processing system that can combine both analog and digital pole / zero circuits and processes for the pet electronics for a combined mr / pet modality . the system can be used in the field of nuclear medical imagining . the system can enable the signal processing hardware to achieve a higher count rate capability than systems employing either an analog circuit or a digital pole / zero filter algorithm employed individually . the lower gain of the apds requires the use of low noise electronics to be able to measure accurate timing of the annihilation photons for a pet modality . in the specific application where an analog charge sensitive amplifier ( csa ) is used to integrate the apd charge derived from crystal scintillation light , an analog continuous reset of the integrator can be achieved by a large effective impedance in parallel with the integrating feedback element , a capacitor . this integrator &# 39 ; s reset time can be set larger than the collection time both to measure the full photon yield and to minimize the current noise density due to the feedback impedance , rf . from a macroscopic signal view , the end result with an apd / crystal - based detector and csa is that an integral exponential rise is shorter than the reset time . this parallel resistor - capacitor ( rc ) results in an exponential signal tail necessarily much longer than that required to the measure the full light emission of the scintillation crystal . although a gated low impedance reset circuit , i . e ., a gated integrator , can be used to reduce the integrated charge signal , the gating logic contains higher frequency signal components that need to be shielded in this specialized application , since the pet detectors are in such close proximity to the receiving mr electronics and are a noise source for the mr modality that must be minimized . for low noise and simplicity for a large number of channels , the integration reset function for this application consists of an analog parallel rc . referring to fig1 , a block diagram of the electrical signal path of an avalanche photodiode based detector using an analog pole / zero circuit combined with a discrete infinite impulse response filter for tail subtraction to improve high count rate operation is depicted . scintillation detector 101 with bias 102 generates an electrical signal . the signal is transmitted to analog pole / zero circuit 103 , which comprises an operational amplifier with passive feedback and gain elements . the analog pole / zero circuit could be any of the recognized types that one of skill in the art could envision to effectively create a circuit with one dominant pole and one dominant zero . circuit 103 has pole / zero function 104 , which can be given according to equation 1 in its continuous laplace transform equivalent form . in equation 1 , s represents the continuous domain complex frequency variable σ + jω , τ i represents [ a single zero , pole cancellation constant , used to cancel the dominant signal tail from the csa reset circuit , and τ 2 represents the substituted circuit single pole time constant after the original pole from the reset circuit has been cancelled by zero , τ i . circuit 103 is connected to cable driver / buffer 105 . the analog pole / zero cancelled signal is discrete - time sampled by analog to digital convert ( adc ) 105 . digital iir filter 107 can be used to improve the count rate performance of the crystal localization / energy algorithm 108 and timing algorithm 109 at high count rates . the localization routine is used to determine which crystal absorbed the gamma photons from a weighted combination of all light sensors associated with the apd / scintillation crystal detector . the number of crystals to light sensors in the apd / scintillation crystal detector is much greater than 1 : 1 for reasons of economic necessity . at a high detector count rate , signal tails from previously detected gamma photons are the source of measurement errors for determining event position , total event evergy , and the gamma photon &# 39 ; s time - of arrival . the time - of - arrival circuit is used to determine if two detected gamma photons are in time coincidence of each other , on the order of 20 ns or less for modern pet scanners . in nuclear spectroscopy , the exponential signal tail caused by an ideal integrator analog reset circuit can be eliminated by applying what is known as a pole / zero circuit in a following gain stages , which is shown in block diagram form in the first half of fig1 . if it is assumed that the scintillation detector signal is of first - order modeled as a signal exponential or pole of value 1 / τ 1 , the long tail resulting from the detector preamplifier can be cancelled by the zero of the pole / zero circuit leaving a remnant pole time constant 1 / τ 2 of the pole / zero circuit . if the csa is implemented in discrete form , the time constant of the resetting pole may be measured and an accurate cancellation is possible for a large number of channels . if the csa is implemented in a custom application specific integrated circuit ( asic ), the reset time constant may be cancelled , not because the absolute time constants are known , but because the lithography and processing cause the component values of the capacitances and effective resistances of the integrator and pole / zero cancellation circuits to track within a small area even though the absolute values may deviate by as much as 50 %. according to one embodiment , discrete - time filters have been developed to emulate their analog continuous counterparts . the analog pole / zero filter described above may also be implemented as a discrete filter that is nearly equivalent to the time - sampled analog pole / zero impulse response given sufficient accuracy of the digital coefficients for the filter . the system can use a combination of analog and digital pole / zero processing to achieve the benefits of both methods when used in a distributed system for a combined mr / pet modality . an advantage of an analog pole / zero cancellation directly at the detector before the signal is transmitted over a transmission cable to the processing unit is that the peak activity level that can be linearly processed with a fixed adc analog input range is higher than if the detector signals are transmitted with slow exponential reset tails . if the long reset tail τ i remains , then the photopeak signal needs to be appropriately scaled so that multiple pileup events do not cause the analog input range of the adcs ( typically 1 vpp or 2 vpp for a typical embodiment ) to be exceeded . a pileup event is defined as a measured gamma photon event that contains at least some of the remnant energy of past scintillation events before previous scintillation events &# 39 ; signals have been reset to within 1 % of the reference signal baseline level . the significance of the pileup events on the time - of - arrival and event localization measurement is best understood by modeling the input signals from the detectors as a random poisson process in time . if only the digital pole / zero is implemented directly from the csa , the highest acceptable count rate is lower than if the digital pole / zero algorithm is combined with the analog pole / zero circuit . in practice , this may necessitate that the 511 kev photopeak signal be lowered up to 5 times compared to an analog pole / zero filter applied to the apd detector signal prior to signal transmission as shown in fig1 . for a large distributed system this may cause distorted signals in the pet electronic signals due to the unrelated modality rf signals from the mr . there can be a remnant signal tail remaining from the analog pole / zero cancellation due to the component tolerances both in the csa and in the analog pole / zero circuit . various embodiments of the system , method , and apparatus can use an analog pole / zero filter to allow an increased signal level at the interface between the pet detectors and processing unit in the pet modality of a combined mr / pet modality . various embodiments of the system , method , and apparatus can use a sum of exponentials approximation to model the remnant signal tail of the detector signal after the analog pole / zero cancellation . in the envisioned embodiment , the statistical mean or expected value of the single pole value of the application specific integrated circuit &# 39 ; s ( asic &# 39 ; s ) ( csa ) reset time constant is used as the expected value of the pole time constant . the remnant signal tail resulting from ac coupling time constants and mismatch of the analog circuits can remain . various embodiments of the system , method , and apparatus can use a digitial infinite impulse response ( iir ) filter implemented with fixed point arithmetic inside a field programmable gate array ( fpga ) to cancel many poles of the signal approximated as a sum of exponentials , which is used as an input to a digital timing algorithm , crystal localization algorithm , and total energy algorithm . the embodiment will reduce measurement errors at single photons count rates of greater than 50 kcps . the analog pole / zero cancelled signal is discrete - time sampled by an adc after appropriate nyquist bandwidth limiting . the digital iir filter is used to improve the count rate performance of the crystal localization and timing algorithms at greater than 50 kcps for the pet electronics in a dual mode mr / pet gantry . various embodiments can include a method that measures the remaining signal tail on a per signal basis during a routine gantry setup and use a least square error fit to tune the digital coefficients of the filter coefficients automatically during gantry setup to optimize the count rate capability of the pet signal path in the combined mr / pet gantry . the optimal coefficients can be determined at low system count rates , less than 20 kcps per signal , where the remnant signal tails can be minimized through an iterative process by acquiring a histogram of each signal tail , automatically readjusting the digital coefficients , followed by subsequent histogram periods . the coefficients are stored in nonvolatile memory for later pet data acquisitions scans at normal and high count rates . the system , according to certain embodiments , is of particular use in a combined mr / pet modality where the narrowband mr electronics generate wideband electromagnetic signal content that is potentially coupled into different signal path points in the pet architecture . the system improves signal quality at the long cable interface and in the alter amplification stages . the analog pole / zero filtered signals can have a higher bandwith due to the substituted pole than the unfiltered csa detector signals in order to improve the signal risetime and time resolution in the pet application . these higher frequency spectral components radiate more easily at the cable interface thus potentially impacting the mri unless effective shielding is implemented . referring to fig2 , a block diagram of the electrical signal path of an avalanche photodiode based detector using a discrete infinite impulse response filter for tail subtraction to improve accuracy at moderate and high count rates is depicted . scintillation detector 201 with bias 202 generates an electrical signal . the signal is transmitted to analog pole / zero circuit 203 , which comprises passive networks and an operational amplifier . circuit 203 is connected to cable driver / buffer 204 . the analog pole / zero cancelled signal is discrete - time sampled by analog to digital converter ( adc ) 205 . digital iir filter 206 can be used to improve the count rate performance of the crystal localization / energy algorithm 207 and timing algorithm 208 at moderate and high count rates . digital iir filter 206 can be a single pole / zero digital filter and can comprise a field programmable gate array ( fpga ) employing a z - transform filter described mathematically in the form of equation 2 , for an ideal single exponential defined signal originating from a csa / scintillation crystal detector combination . in equation 2 , z represents the complex frequency variable e st , k 1 represents a constant coefficient , k 2 represents a scaling coefficient , k 3 represents the scaling filter coefficient associated with the last discrete output value of the iir filter . in the embodiment shown in fig2 , the system count rate is low enough that the dynamic range of the adc is not approached at the scanner maximum count rate . the analog pole / zero circuit , at this point , becomes unnecessary , if the csa integrator is assumed linear . the digitally implemented pole / zero filter is used to effectively cancel both the integrator circuit reset time and the ac coupling time constants from the apd / scintillation crystal based detectors . fig3 depicts one possible embodiment of the iir filter . the magnitude of the fourier transform of the infinite impulse response filter , h ( z ), used to cancel the single pole exponential tail from an an ideal avalanche photodiode / charge sensitive amplifier based detector . fig4 depicts the phase response of the fourier transform of one embodiment of the infinite impulse response filter , h ( z ), used to cancel the single pole exponential tail from an ideal avalanche photodiode / charge sensitive amplifier based detector . a processor as used herein is a device for executing stored machine - readable instructions for performing tasks and may comprise any one or combination of hardware and firmware . a processor may also comprise memory storing machine - readable instructions executable for performing tasks . a processor acts upon information by manipulating , analyzing , modifying , converting or transmitting information for use by an executable procedure or an information device , and / or by routing the information to an output device . a processor may use or comprise the capabilities of a controller or microprocessor , for example . a processor may be electrically coupled with any other processor enabling interaction and / or communication there - between . a processor comprising executable instructions may be electrically coupled by being within stored executable instruction enabling interaction and / or communication with executable instructions comprising another processor . a user interface processor or generator is a known element comprising electronic circuitry or software or a combination of both for generating display images or portions thereof . a user interface comprises one or more display images enabling user interaction with a processor or other device . an executable application comprises code or machine readable instructions for conditioning the processor to implement predetermined functions , such as those of an operating system , a context data acquisition system or other information processing system , for example , in response to user command or input . an executable procedure is a segment of code or machine readable instruction , sub - routine , or other distinct section of code or portion of an executable application for performing one or more particular processes . these processes may include receiving input data and / or parameters , performing operations on received input data and / or performing functions in response to received input parameters , and providing resulting output data and / or parameters . a user interface ( ui ), as used herein , comprises one or more display images , generated by a user interface processor and enabling user interaction with a processor or other device and associated data acquisition and processing functions . the ui also includes an executable procedure or executable application . the executable procedure or executable application conditions the user interface processor to generate signals representing the ui display images . these signals are supplied to a display device which displays the image for viewing by the user . the executable procedure or executable application further receives signals from user input devices , such as a keyboard , mouse , light pen , touch screen or any other means allowing a user to provide data to a processor . the processor , under control of an executable procedure or executable application , manipulates the ui display images in response to signals received from the input devices . in this way , the user interacts with the display image using the input devices , enabling user interaction with the processor or other device . the functions and process steps herein may be performed automatically or wholly or partially in response to user command . an activity ( including a step ) performed automatically is performed in response to executable instruction or device operation without user direct initiation of the activity . an object or data object comprises a grouping of data , executable instructions or a combination of both or an executable procedure . the technology can take the form of an entirely hardware embodiment , an entirely software embodiment or an embodiment containing both hardware and software elements . in one embodiment , the invention is implemented in software , which includes but is not limited to firmware , resident software , microcode , etc . furthermore , the invention can take the form of a computer program product accessible from a computer - usable or computer - readable medium providing program code for use by or in connection with a computer or any instruction execution system . for the purposes of this description , a computer - usable or computer readable medium can be any apparatus that can contain , store , communicate , propagate , or transport the program for use by or in connection with the instruction execution system , apparatus , or device . the medium can be an electronic , magnetic , optical , electromagnetic , infrared , or semiconductor system ( or apparatus or device ) or a propagation medium ( though propagation mediums in and of themselves as signal carriers are not included in the definition of physical computer - readable medium ). examples of a physical computer - readable medium include a semiconductor or solid - state memory , magnetic tape , a removable computer diskette , a random access memory ( ram ), a read - only memory ( rom ), a rigid magnetic disk and an optical disk . current examples of optical disks include compact disk - read only memory ( cd - rom ), compact disk - read / write ( cd - r / w ) and dvd . both processors and program code for implementing each as aspect of the technology can be centralized and / or distributed as known to those skilled in the art . the above disclosure provides examples and aspects relating to various embodiments within the scope of claims , appended hereto or later added in accordance with applicable law . however , these examples are not limiting as to how any disclosed aspect may be implemented , as those of ordinary skill can apply these disclosures to particular situations in a variety of ways . although the present invention has been described in considerable detail with reference to certain preferred versions thereof , other versions are possible . therefore , the spirit and scope of the appended claims should not be limited to the description of the preferred versions contained herein . the reader &# 39 ; s attention is directed to all papers and documents which are filed concurrently with this specification and which are open to public inspection with this specification , and the contents of all such papers and documents are incorporated herein by reference . all the features disclosed in this specification ( including any accompanying claims , abstract , and drawings ) may be replaced by alternative features serving the same , equivalent or similar purpose , unless expressly stated otherwise . thus , unless expressly stated otherwise , each feature disclosed is one example only of a generic series of equivalent or similar features . any element in a claim that does not explicitly state “ means for ” performing a specified function , or “ step for ” performing a specific function , is not to be interpreted as a “ means ” or “ step ” clause as specified in 35 u . s . c § 112 , sixth paragraph . in particular , the use of “ step of ” in the claims herein is not intended to invoke the provisions of 35 u . s . c § 112 , sixth paragraph .
a data processing process and embodiment for optimizing the signal path for multi - modality imaging is described . the embodiment and process optimizes the signal to noise ratio in a positron emission tomography signal path utilizing scintillation crystals , avalanche photo diodes , and charge sensitive preamplifiers in a dual modality mri / pet scanner . the dual use of both and analog pole zero circuit and a digital filter enables higher signal levels or a fixed adc input range and thus a higher possible signal to noise ratio in the presence of significant pileup caused by high positron activity . the higher signal to noise ratio is needed in the pet signal architecture , because of the presence of non - modal time varying electromagnetic fields from the mr , which are a significant source of noise for the wideband pet signal modality .