CA2587804A1 - Modular multi-modal tomographic detector and system - Google Patents

Abstract

A multi-modality detection system and method for detecting medically-related conditions is disclosed. In some respects, the system and methods rely on at least two different modalities for imaging a region of interest including a patient organ such as the breast, brain, or other object within the region of interest. The two or more modalities are enabled with respective detectors as described herein and a respective output of each is collected and formed into a combined (fused) output representative of the plurality of different imaging modalities to enable imagine, diagnosis, study, or treatment of the medical condition.

Description

MODUI.Aiz MULTI-MODAL TOMOC3RApHIC DETECI'ORAND SYSTEM
1. Technical Field [00011 The present disclosure relates, in generai, to gamma ray and x-ray detector systems and signa,l processing for nuclear medieine gan una cametas, single photon emission toniograph}r (SPECr), positron emission tomography (X'E1), x-ray computed tomography (GT), digital radiobgy, x iay nwrnrrx~graphy, and other limited field of view gainma ray and x-ray detection and signal processing Q,stnunentadon.

II. Related Applications [0002] The present application is a continuation in part (CIP) of and claims prioriocyto U.S.
Pat. App]icamion Serial Number 11/074,239, entitled "Breast Diagnostic Appa:atus for Fused SPEGT, PET, X-ray CT, and Optical Surface Imaging of Breast Caneer," filed on March 7,2005, which is hereby incorporated by reference.

III. Backgraund 100031 'I'his applicatian relates to the field of gamma ray inaging, nuclear SPECT imaging, PET krraging, x-ray CT iumaging, digiral radiography (DR) imaging, x-ray mammography. oPdcal imaging, optical fluorescence irnaging, small field of view imaging deteccors and probes, and fused irniltimodality imaging.

[0004] In breasc iinaging and screening, x-ray mammography is being used as a screening tool for women over the age of 40 years. During the screening process, 40% of women have dense Pater~ApvltQZtia~e breast or suspicious breast indications for cancer. The radiologists reading these mammograms have difficulty reading the dense breast x-ray nrainmograms. A better method is needed for detecting cancer in dense breasts. Currently 8 out of 10 biopsies done on these patients indicate a false positive from x-ray rnaixunography.

[0005] To improve the detection of brean cancer in women having dense breasu, a combination of molecular cellular functional itnages and x-ray density irrrages of the breast is needed.
Radioisotopes such as Tc-99m Sestamibi and positron isotopes such as FDG-F18 uptake in cancerous cells more rapidlythan normal cells. Tc-99rriSestamibi molecules uptake in tlie rnitochondria of the ceU. Cancerous ceIls have more niitochondrial activity in comparison to normal surrounding cells. Simi7arlyFDG F-18 uptake in cancerous cells is due to more glucose nietabolism.
'I'he breast cancer cells uptake these isotopes more rapidly than the surrounding nonnal tissue. 'Ihus, cancerous cells will enut more gamma rays as compared to norrrral cells.

[0006] In order to build a more sensitive and specific breast inraging device, the device must have higher spatial resolution and better contrast sensitivity than whole body imaging systems.
Also the device must provide rhe locacion of the radioisotope distributions and anatoniical x-ray density of breast tissues. In addition, the device must provide anatomical surface imaging of the breast superimposed with the radioisotope distributions and x-ray density of breast tissues and micro calcifications in three dimensions.

[0007] Today, projection x-ray mammography is used to detect breast density by compressing the breast tissm causing pain in some instances to the patient undergoing the manvnogra.phic exam. Once this exam has been completed and a dense breast indication has been found, there is not an easy ahernative except to biopsy the breast tissues by surgery.

[0008] Scintigraphy has been used in conjunction with whole body gamma cameras wit.h Tc-99m Sestamibi, but the sensitivity specificity drops below 40% when cancerous lesions ane less PawrA ppl'ieztian than 2 cm in size. Ultrasound also maybe used in the case of dense breasts but the procedure is very operator dependent. Therefore, there is a need for a more sensitive and specific breast imaging system which is comforrable for the patient and can provide true three dimensional information regarding potential breast cancer at the no.olecular level before anatomical changes occur. If there is a positive finding that breast cancer exisus, then the system should provi.de three dimensional morphological infonnation regarding the location of the cancer for surgical biopsy and rapid therapy.

IV. Sumrnary [0009] A Inulti-rnodality detection system and method for detecting medically-related conditions is disclosed. In sorne respects, the system and naethods rely on at least two different modalities for imaging a region of interest including a patient organ such as the breast, brain, or other object within the region of interest, The two or more modalities may be enabled avith respective detectors as described herein and a respective output of each may be collected and fonnied into a conibined (fused) output representative of the plurality of different -maging modalities to enable imagine, diagnosis, study, or treatment of the medical condition.

100101 The present disclosure comprehends sixnultaneous application of more than one type of rrudical imaging (or imaging modality) to an olgan or portion of a subject's body. For example, various imaging niodalities that can be employed by the present srtems and methods include gamma detection, X ray detection, SPECI, PET, and other modalities that are used in tomographic systems for the purpose of detecting, sensing, generating images, diagnosing, locating, and treating a physiological or medical condition. Some conditions comprehended hereby include demmtia in its various forms, for example, breast diseases such as breast cancer, diseases in the Paterrt A ppfraxtian huitxin taead and brain, including neuno-degenerative diseases, P,lzheimer's disease, Pick's disease, Huntington's disease, and mnhiple infarct conditions.

100111 The present system and methods provide for simuhaneous or substantially simuhaneous measurement and detection of a physical event to cause a sensor to respond thereto.
By proper applicatiion of such a sensor it is possible to construct a detector apparatas for detecting the e+rern or phuality of events an image of an underlying physiological object or feature of the object, conditiorn, disease, contrast agent, or bodypan or organ may be obtained. Receiving additional inforcnation from more than one imaging detector representing more than one imaging modality can provide an inxproved and better resolved and more clinicaily rr-eaningful image of a subject or condition under investigation.

[0012] Some embodiments of the present disclosuie are directed to a medical imaging apparatus, comprising a first detector contributing a first imaging modality for detecting a medical condition in a region of interest; a second detector contributing a second imaging modalityfor detecting said medical condition in said region of interest, said second imaging rnodalitybeing diffcrent than said first imaging modality; and a structural frame supporting both of said first and second detectors, said frame ma+*mah+irig a substantiaIlyfixed relative positioning berween said detectors with respect to one another while allowing relative motion between said detectors and said region of interest.

100131 Other embodiments are directed to a method for generating a multi-modal image for detecting a medical condition, comprising imaging a region of interest using a first imaging modaGtq for detecting said condition; imaging said region of interest using a second inaging modaliryfor detecting said condition; mechanically fixing respective detectors for said first and second imaging modalities to a structural support frame so as to substantiallyfix said respective detectors with respect to one another while allowing relative motion between said detectors; and PatenrAppliactiai combining respective outputs of said fkst and second imaging modalities so as to form a muhi-modal combined output thereof indicative of said condition.

V. Brief Description of the Urawiags 100141 The present systems and methods can be better Mustrated and understood in view of the accompanying drawings, in which:

[00151 FIG,1 dlustrates a top fronral view of an appamtus utilized by a breast scan system as descnbed herein;

100161 FIG. 2 ilhutrates a perspective view of an apparatus utilized bya breast scan system showing a patienz on a patient table as described hemin;

[00171 FIG. 3 illustra,tes a system block diagram showing an architecture as descrbed herein;

[00181 FIG. 4 illustrates a pesspective view of an apparatus showing a patient tiked to one side on a patient table as described herein;

(0019) FIG. 5bLStrates a perspective view of a patient on a patient table, and illu.nra.tes an upper outer quadrant gatnma curved detector associated with a breast scan system as described herein;

[0020] FIG. 6 illusaates an exploded view of an upper outer quadrant gamma curved detector shown in FIG. 5;

(00211 FIG. 7 iIlustraties a top p[an view of an upper outer quadrant gannria curved detector shown in FIGS. 5 and 6;

Pate~Appd'~tian [0022] FIG. 8 illustrates a perspective view of an upper outeu quadzant gamrna curved detector, a central breast curved gamma detector, and a X-ray source and detector in an imaging system;

[0023] FIG. 9 illustrates a front elevational view showing a position of the irnaging components of FIG. 8 with respect to a patient;

[0024] FIG, 10 illustrates a left end view showing a position of the imaging components of FIGS. 8 and 9 with respect to a patient;

[0025] FIG. 11 illustrates a front elevational exploded view of an upper outer quadrant gamrm curved detector showing its position with respect to a patient;

[0026] FIG. 12 illustrates a left end exploded view of an upper outer quadrant gairuna curved detector showing irs position with respect to a patient at the beginning of a tomographic scan;

[00271 FIG. 13 illustrates a left end exploded view of an upper outer quadrant gamma curved detector and illustrates its position with respect to a patient partially through a tomographic scan;

[0028] FIG. 14 illustrates a left end exploded view of an upper outer quadrant gamma curved detector and illustrates its position with respect to a patient at the end of a tomographic scan;
[0029] FIG. 15 illusuates a perspective view of a central, breast curved gamnia detector, a central breast curved coincidence gamma detector, and a X-ray source and detector as described herein;

[0030] FIG. 16 illustrates a left end view and a side view of an upper outer quadrant gamma curved detector and a central breast curved coincidence ganuna detector of a breast scan system as descnbed herein;

Pate~Ap~
[0031] PIG. 17 illustrates nmicno PET imaging Eies of response produced bya PET
imaging system as descnbed herein;

[0032] FIG. 18 illustrates a perspective view of a single photon and coincidence garxuna decector uu'lized bya breast scan system as descnbed herein;

[0033] FIG. 19 ilhutrates an end view of the single photon and coincidence garrum detector shown in FIG. 18;

[0034] FIG. 20 iJlustrates a perspective view of a detector module utilizcd by the single photon and coincidence gaaurra detector shown in FIGS. 18 and 19;

[0035] FIG. 21 illuscrxtes a front elevational view of a detector module shown in FlG, 20 and a perspective view of the pixelated gamrna detector elensents contained therein;

[0036] FIG. 22 illustrates a front plan view of a patient showing a central breast scan and illustrating a representative position of the single photon and coincidence gamrna detector as described herein;

[0037] FIG. 23 ilhlstrates an end view of a patient on a patient table showing an upper outer quadrant breast scan and a representative position of a single photon and coincidence gamtm detector as described herein;

[0038] FIG. 24 ilhustrates a front plan view of a patient showing a X ray scan of a breast and representative positions of the X-ray source and detector during a scan;

[0039] FIG. 25 Alustrates an end view showing breast scan data acquisition orbits and recoristtuction of radioisotope disnnbutions in a breast utilizing the breast scan system as descnbed herein;

[0040] FIG. 26 illtistratss an end view showing breast scan data acquisition orbits and reconstcuction of X-ray transmissions in a breast utilixing a bn:ast scan system as described herein;

Puter&Appliazrian [0041] FIG. 27 Mustrates a schematic diagram showing fusing of muhimodalityiunages by utilizing a breast scan system as descrnbed herein;

[00421 FIG. 28 illusttates a front elevational view of a patient on a patient table and illustrates stereo-tactic biopsy, rninimalty invasive surgery, and ixnage-guided therapy using muhimodality images produced by a breast scan system as descnbed herein;

100431 FIG. 29 i[lustrates a perspective view of a rrailti-modal tomographic modular irxra.ging detector utilized in some enixxhrwnts hereof;

[0044] FIG. 30 illustrates an exploded component view of a multi moda]
tomographic modular irnaging detector, 100451 FIG. 31 illustrates a view of an exemplarypbrilated 2D scintillation cryrtal array;
[0046] FIG. 32 iflusuates a view of a 2D micro channel plate with a 2D matrix of anodes;
[0047J FIG. 33 MLSttxtes a block diagrm shoa+ing an exemplazy independent channel processor cascaded with a multti-modality tomogrxphic modular imaging detector, [0048] FIG. 34 iUu,strates a functional block diagmm of an exemplasy independent channel event processor for the multi-modality tomographic modular imaging detector, [0040] FIG. 35 iIlustrates a functional block diagram of an exemplary rnatric event processor for the multi modality tornographic rmodular inWing detector, [0050] FIG. 36 iJiastrates an exemplarycollimation and radiation shielding for the multi-modalitytomographic rnodular imaging detector, [0051] FIG. 37 dlustrates an exemplaryembodirnent of a curved detector assembly using the multi-modality tomographic modular detector modules; and [0052] FIG. 38 illustrates an exemplary coincidence imaging with two curved detector asscmblies of a multi-modality tomographic modular deteetor system.

AatetAppliUtian VI. Detailed Deseription [00531 Referring noarto the Figures where the illustrations are for the purpose of describing embodiments of the present invention and are not intended to limit the invention disclosed herein, FIG. 1 illustrates a top frontal view of an apparatus that may be utilized by a breast scan system. As shown in FIG. 2, the patient 10 lies prone and slighrly tihed to one side to all~.ow full extension of the bxieast through a left breast hole 8 or right breast hole 7, The bneast is scanned with an anatomic specific irnaging central breast curved gamm detector Tfor single photon emission compuced tomography (SPEC.'I). Radioisotopes are injected into the patient 10 and emitted radiation is detected by the central breast curved garruna detector 1. The breast scan systcm also has an x-raysource 5 and an x-raydetector 6, The x-ray source 5 transmits x-rays through the breast of the patient 10 which are detected bythe x-raydeuctor6. The x-raysource 5 and x-raydetector 6 are rotated around the patient's breast on a rotate table 2. Also the central breast curved gamma detector 1 is mtated around the patient's breast on rotate table 2.

[0054] The upper outer quadrant gamma curved detector 3 can be positioned to itrrage the upper oucer quadrant of the breast to the axiDa. The upper outer quadrant garruna curved detecmr 3 collects radioisotope infortnatiion from the patiern's breast area where the centtal breast curved gamma detector I cannot be positioned. The sliding detector carriage 9 allows the imaging components to be trarw,slated horizontally from the left breast hole 8 or to the right breast hole 7, and vice versa, to image the respective breast.

[0055] In FIG. 2, the patient 10 is shown lying prone and slightlytilted to one side on breast insaging patient table 4 and over left breast hole 8. The patient's breast is cxtended by gravity for imaging. The patient is injected with a radioisotope which accumulates in cancerous tissues of the breast more rapidlythan nonnil tissues, The central breast curved gamma detector 1 detects I'aterAppliazttmi gamma rays emitted from the radioisotope distnbutions. The central breast curved gamina detector 1 is designed to anatomieallyfit close to the shape of the central breast to collect gamma rays being emitted. The central breast curved gatnma detector 1 is rotated around the patient's central breast by rotate table 2. The upper outer quadrant gamma curved detector 3 is positioned around the patient's thorax to collect garnrna rays from the upper outer quadrant of the breast co the axilla. 7he breast anatomy is a complex imaging atea and the system is designed to image the entire breast including the lymph nodes. The upper outer quadrant ganuna curved detector 3 can be positioned three dimensionally around the patient's thorax with vertical, horizontal, traverse, and oscillations to collect data while being very close to the patient 10.

[0056] As shown, x-ray source 5 and x-ray detector 6 are mounted to the rotate table 2.
This allows for x-ray micro computed tomography of the breast. The x-ray sotuce 5, x-ray detecicor 6, and central breast curved gamma detector 1 are all positioned around the patient's breast on the Ivtate table 2 to acquire high cssolution single photon enzission cornputed tomographic (SPECr) images and x-ray high resolution computed tomograQhy (Cl) images of the breast. In addition, the slidmg detector carriage 9 allows imaging of the left breast through the left breast hole 8 and then trumlates to right breast hole 7 for repositioning of the patient for right breast imaging.

100571 Referring now to FIG. 3, the overall architecture and system structure is shown.
Gamuna rays are detected by either the central brean gamma curved detector(s) 1 and/or the upper outer quadrant gamrna curved detector 3. These detectors can collect ga.mrrra rays enutted from single photon enutting isotopes, such as Tc-99rn, or posiEron emitting isotopes, such as F-18. When using the positron ernitting isotopes, coincidence detection is used to collect and determine the angle of the pair of 180 degree opposed garrum rays emitted from a positron annihilation. The central breast SPEG"r'/PET DAQ block 15 controls and acquires both single photon gamma rays and coincidence gamma rays from the central breast gamma curved detectors 1 to form isotope I'atatApplaa:tion projection images. The central breast motion contnoller 17 controls the geometric positioning of the central breast gamuna curved detectors 1 including, rotation, vertical, radial, oseillar,e, and tilt positioning. The upper outer qua,dram SPEGT/PET DAQ block 16 controls and acquires both single photon ganima rays and coincidence gamma rays fx+om upper outer quadrant curved gamma detector 3 to form isotope projection images.'Ihe upper outer quadrant motion controIler 18 controls the geometric positioning of the upper outer qvadrant gamma curved detector 3 including rotation, vertical, radial, oscillate, and tih positioning.

[0058] As shown, x-ray CI' DAQ 20 interfaees w[th the micro C.'I' a-ray source 5 and x xn-y detector 6 to acquire projection x-ray images thnough the breast anatatny. The n-iicro C.T X-ray source 5 and x-ray detector 6 are positioned bythe x-ray CT motion controller 38 for x-ray micro CT of breast densities. The x-ray GT DAQ block 20 controls and acquires data from the micco CI' x-ray source 5 and the x-ray detector 6. The x-ray CT DAQ 20 controls the x-ray detector 6 to generate projection views thmugh the breaast anatomy and form two dimension frames of attenuated x-rays. For optical irnages of the breast, optieal breast cameras 11 are attached to respective micro CT x ray source 5, x-ray detector 6, cem.ral breasi gamma curved detectors 1, and upper outer quadrant gamina curved detector 3. The optical DAQ 21 controls the optical breast cameras 11 to generate optical views of the breast for spectral irrrage of the breast at various wavelengths. The breast system reconstnuction and control computer 19 controls and coIlects data from respective data acquisition (DAO) and motion controilers. SpecificaIly, the projection gamrrra images, coincidence gamma images or positron emission tomography (pE'I) images, x-ray projection images, and optical iIrrages are processed by the breast Yeconstruction and control computer 19 to form micro SPECI'voim-gs, micro PET volumes, micro CT volumes of the breast anatomical density and radioactive isotope uptake in breast tissues. Also the breast reconstruction and control computer 19 geometrically overlays the optical views of the breast in co-registration with micro SPECT, micro Pate~Applioxiip:
PET, and micno C.T three dimensional information. The three dimensional breast data from the respective inodalities of micro SPECT, micro PET, micro GT, and optical surface iznage spectsvsris are combined together or fused on the breast display and analysis workstation 22.

[00591 Referring now to FIG. 4, the patient 10 may lie on the patient table slightly tilted to one side to allow fuD. breast estension by gravity into the left breast hole 8.'ihe patient nray be disposed in other configurations and positions with respect to the table, platform, or support strnu-tuze or member. For example, the patient may be upright, in a standing or sitting position, wh~7e the patient's breast is suitably disposed within an imaging negion of interest that allows imaging of the breast. The patient and the imaging system and debectors ane thus oriented in a convenient and physically cornpatible way to obtain the multi-moda[ images as described herein, and not necessasily constrxining the patient or the imaging apparatus to any parricular absolute or relative orientation.

[00601 The sliding detector carriage 9 can be positioned interactively by an operator for alignment on the center of the left bneast. The scans can then be done on the left breast, Also shown is the upper outer quadrant gaz:una curved detector 3 which can be positioned to image the upper outer cluadtant of the breast. The upper outer quadrant gamma curved detector 3 can be positioned by the upper outer quadruYt mtion controller 18 in an elliptical and oscillatory motion to obtain enough views io tomogrdphically reconstruct the upper outer quadrant region of the breast.

10061j In FIG. 5, the patient 10 is shown lying prone and slightlytilted to one side wirh her left breast extended into the left breast hole. The centiral br+east curved gamina detector 1 is shown mounr,ed to an oscillate positioner 14, a vertical positioner 12, radial positioner 13, rotate table 2, and to the sliding detector caniage 9. 'Ihe x-raysource 5 and x-ray detector 6 are also maneuvered about the patient's breast vvith their respective vertical positioners on rotate table 2. The upper outer quadrant gamina curved detector 3 is positioned around the patient's breast and thorax.

PatftAppkb~ran The upper outer quadrant ganuna curved detector 3 is maneuvered with its respective oscillate positioner 14, radial positioner 13, vertical positioner 12, traverse positioner 39, and sliding detector carriage 9.

[0062] Referxing now to FIG. 6, the upper outer quadrant gamma curved detector 3 is shown close to the patiern's chest and upper outar quadrant of the patierns breast. The upper outer quadrant gamma curved detector 3 is positioned close to the patient's breast anatomy via oscillate positioner 14, radial positioner 13, vertical positioner 12, and transverse positioner 39 mounted on sliding detector cartiage 9.

[0063] In FIG. 7, the upper outer quadrant gamma curved detector 3 is shown being positioned with coordinmd motion via oscillate positioner 14, radial positioner 13, vernical positioner 12, and tiansverse positioner 39 mounted on sliding detector caniage 9.

[0064] As shown in FIG. 8, the apparatus utilized to obtain nniltiple angular radioisotopes views, x rayviews, and optical spectrum views of the breast is illusrsated.
For the central breast scan, the central breast curved gamma detector 1, x-ray source 5 and x-my detector 6 are rotated around the breast on rotate table 2. 'I'he central breast curved gamma detector 1 x-ray source 5 and x-ray detector 6 have a respective oscillate positioner 14, vertical positioner 12, and radial positioner 13 to be moved around the central breast in a coordinated motion to collect anatomic specific views. The posidon orbits and respective oscillations of respective components allow the central breast curved garnnra detector i to be positioned close to the breast without touching the breast to improve spatial resolution of and sensitiviryto radioisotope distnbutions within the breast.
Also geometric and temporal x-rayviews of the breasc can bc done with x-ray source 5 and x-ray detector 6 being positioned via their respective vertical positioners 12, radial positionexs 13, and rotate table 2. The position of the upper outer quadrant gamma curved detector 3 can be synchronized with cent.rdl breast imaging components.

AateratAppliaaaz [00651 Referring now to FIG. 9, the system concept is shown from aside viewwirh the patient 10 lying pxone and slighttytiled to one side with full breast extension by gravity. The x ray source 5 and x ray detector 6 are shown with their respective vertical positioners 12 and rotate table 2.

[0066] In FIG. 10, the central breast curved gamtna detector 1 is shown collecting projection view data of radioisotope distributions while being positioned close to the breast anatomy. Also the x-ray source 5 and x-ray detector 6 are also positioned on cornmon rotate table 2.

An optical breast camera 11 is shown to take temporallysynchionized views of the breast's optical reflections, trdnsmissions, and fluorescence at various specttums or wavelengths. One use of the optical views is for breast surface registration with respective x ray transmission and radioisotope views.

[0067] Referring now to FIGS. 11,12,13,14, variom positions of the upper outer quadrant gamma curved deteeuor 3 are shown collecting gamma rays from radioisotope distributions within the breast and lyiWhnwdes located close to the breast. The upper outer quadrant area of the bieast is the location where 50% of cancess occur. FIG. 14 shows views from the back and left side of patient; FIG.11 from the left side of patient and breast; FIG. 12 from the left front side of chest wall and breast; and FIG. 13 from the left back side of chest wall and breast.

[0068] In FIG. 15, the central breast curved coimcidence gamxna detector 23 is shown to allow coincidence detection of positron emitting isotopes, like F- 18. The cenual breast curved gainma detector 1 and central breast curved coincidence gamma detector 23 are operated with temporal coincidence window between each event eollected on the respective detector to form a line of response (LOR) between detector elernents. The central breast curved coincidence gamma detector 23 is also rotated on rotate table 2 and can be positioned with its respective positioners.
Also, the central breast curved coincidence gamma detector 23 can be used for single photon Au~App&~rtiat gamtna detection and woxic in concert with central breast curved garruna detector 1 to form SPECI' inrage projections improving sensitiviny uid specificity of the imaging system.

10069J Referring now to FIG. 16, an exempLuy cenual breast curved coincidence gmnma detector 23 inay be used to operate in coincidence with the upper outer quadrant gamma curved detector 3. This allows for positron imaging of the upper outer quadrant for detection of cancer and lymph node uptake of radioisotope.

[0070] In FIG. 17, the coincidence licxs of response 24 are shown betwven respective breast curved single photon and coincidence gamma detectoss 25. Also the entire breast voltune can be isnaged with translation, rotation, oscillating curved ganuna detector niotion 26.

[0071] As shown in FIG. 18, the breast curved single photon and coincidence gamma detector 25 may be comprised of bxeast curved single photon and coincidence gannma detector moduk(s) 27, '1 he modules 27 are mounted to fonn an anacomic breast shaped curved detector. The breast curved single photon and coincidence gam:xra deteccor module 27 can efficiently iunage lower energy single photon emitting isotopes, such as Tc-99m, at 140.5 KeV as well as 511 KeV
coincidence gamina rays from positron ernitters, such as P-18. DOhen ineaging positron emitters, two breast curved single photon and coincidence garntna detectorrs 25 rnay be operated in coincidence nzode facing each other, as shown in FIG. 17.

[0072] Refeffing now to FIG. 19, an exeinplarybreast curved singk photon and coineidence gamma detector 25 is shown and includes a plurality of niukiple breast curved single photon and coincidence gamma detector modules 27.

[0073] In FIG. 24, the major components of an exemplary breast curved single photon and coincidence gamma detector xnadule 27 are shown. GatrIItta rays and X rays enter a module 27 via ganuna and coincidence collimator 29. The collimator mechanicalty focuses garnma rays for a conmnon set of angles. In an exemplary preferned embodiment, parallel hole collimation may be PQ=ApphCdt1C11 used to allow imaging of single photon emitting radioisotopes. The collimation provides the spatial resolution for SPECT irnagrng. In 511 KeV positron gamma ray imaging, the collimation acts as an anti-scatter grid to reduce down-scatter radiation from 511 KeV interaction in patient. The collimation may be designed with high resolution pammeters and along with positioning of the detector closer to patient provides greatly irnproved spatial resolution and isotope sensitivity.
Pixelated ganuna detector elements 28 or pixilated scintillation crystals are used to provide high resolution iunages. The pixelated array in this eaemplary embodiment are interposed between the ganuna and coincidence collimation 29 and low profile mi.cro channel amplifier 30. The pixelated gamma detector elements 28 convert garnma rays into visible light. The low profile micro channel amplifi~er 30 converrs the light to electrons that are amplified. The single and eoincident gamrra DAQ electronics 31 convert the amplified electrons from the low profile micro channel amplifier 30 to digital signals representing geometric position, energy level, and tirne of ganuna event interaction with breast curved single photon and coincidence detector module.

[0074] As shown in FIG. 21, an exernplarypixelated ganvria detector elements 28 are illustrated and a side view of the breast curved single photon and coincidence gamma detector module 27 are shown. The pixelated gamma detector elements 28 channel the scintillation light down independent channels and allow for high count rate data acquisition with multiple events qcciuring withirl the pixelated array. The scpta between the respective pixels rnay be designed to allow shaping of light distnbutions for high spatial and energy resolation of events in pixels with adaptive weighted positioning algorithms in the single and coincident gaInma DAQ electronics 31.

[0075] Referring now to FIG. 22, an exemplary breast curved single photon and coincidence gamma detector 25 is shown positioned ebse to the central breast anatomy allowing for generation of tomographic views of the breast. The breast single photon and coincidence ganaxxn detector modules 27 may be placed in a curved configtuation to al]ow close view of the breast PaoeraApplinuiaq witlaout touching the breast. The breast curved single photon and coiricidenee gamma detector 25 may be geometrically maneuvered by positioners and motion control systexns.
Also shown is a focused coIIimauon system 29 to view radioisotope distributions.

100761 In FYC',. 23, the breast cumd single photon and coincidence gamma detector 25 is shown generating views of the upper outer quadrant of the patient's breast.
Each of the breast single photon and coincidence detector modules 27 pxnvides a tomgraphic view with unique rotation and oscillation about the outer side of the patienc's breast, chest and back while the patient 10 is lying pmne on patient table 4 with breast extended via gravity. As nyentioned above, this represents an exemplary embodimenz, and other physical absolute and relative orientations of the patient, her breast, and the imaging system are possible, such as by imaging the breast wuh the patient in an upright, seaoed or standing position, or whik the patient lies on her back with the unaging detectors substantially above the patient.

100771 Referring now to FIG. 24, x-ray source 5 and x-ray detecoor 6 are shown generating a fan/cone beam through a patient's breast. Different views am shown to illustrate the exemplary positions of the x ray soluce and detectur around the patient's breast. The plurality of views allow reconstraction of x rayviews to form three d'smensional tomogsaphic slices of the breast's x raydensiaes.

(00T8] In FIG. 25, exemplaty reconsmicted tomographic images are shown fnom the use of progiamunable detector orbits 32, oscillating curved gamma detector orbiu 33 and mconstructed SPEt,'Y' and PET itnages 34 from oscillating orbits. The programmable orbits are adjustable to a patient's size and respective anatomyto obtain optimized spatial resolution and high sensiuviry iunages of radioisotope distributions. Unique reconstruction tomographic processing maybe uulized to produce high clualitYy imaging with these unique views in space.

PaMAppG2zda:
[0079] Irt FIG. 26, exernpluyreconstiueted tomographic images are shown from the prograncunable detector orbits 32 and x-ray source and detector orbits 35 and reconstTVCted x-ray CT image from oscillating orbits 36. I-Iere again, unique reconstruction tomographic processing may be uulized to produce high quality imaging with these unique x-ray views in space.

100$01 Referring now to FIG. 27, an exemplary breast syscem display and analysis worktation 22 combines or fuses images obtained from at least a first and a second icrraging modalicy. '11m radioisotope tornographie images from single gancuna photon emitters with micro SPEG'I', positron emitters with coincident gamrna rays for micro PET, combines with x-ray density images from x-ray micro CT and optieal surface vcm for optical surface spectnum to form fused images of the breast.

[0081] In FIG. 28, an exeinp]a.ty illustrative biopsy or surgical instrument 40 is shown being guided into the pat,ient 10 and mechanically positioned with the stereo-tactic image guided holder 41. The bneasc system dispkay and analysis workstation 22 genexates interactive image guide infonnation to align the stereo-tactic image guided holder 41 while patient 10 is lying prone and slightlytilted on breast imaging patient table 4. The patient and imaging apparatus may also be in other reGtive orientations as discussed above. Also shown are the other basic multiunodality irraguq components of x-ray sourice 5, bleast curved single photon and coincidence gamiraa detector 25, and rotate table 2 to generate images for biopsy, surgical removal, or therapy of breast cancer, The breast cliagnostic apparatus for fused SPEGT, PET, X-ray CT and Optical Surface Imaging of the breast descn'bed herein is a unique multinnodality imaging dcvice to uniquely scan the patient's entire breast, or subsrantiallythe entire breast, for the presence of cancer or other medical conditions.

[0082] FICY. 29 illustrates a dual modality detection module 291 in one exemplary configuration. The dual modality detection module 291 is designed to detect gamma iays (energetic 1$

Paae&Applaaxaw photons) from single photon nuclear isotopes and coincidence photons fnom posstron emiting isotopes. The module is constructed to allow configurations of curved detector arrays for anatonuc specific unaging. The module contains components to detect the position, energy, time of the gamxna ray detected by module for both single photon emission tomography (SPECI) and positron envssion tomography (PE'I). Also a set of modules my be configured to perform coincidence detection for positxon emission tomography (PE'I).

[0083) FIG. 30 shows some rnain components and assemblies of an exemplary dual modality detection niodule. The present disclosure can be extended beyond two modalities, to r.hnee or more modalities fused for the ixnaging of a medical condition and assisting the diagnosis or treatment of the same. The xnodule 301 is conlposed of a collimator 302, crystal housing radiation shield 303, pirilated scintillation crystal and optical coupling 304, micro channel plate aniplifier 305, amplifier radiation shield housing 306, event processing chamel cards 307, and event processor backplane 308.

[00841 The collimator 302 allows for colliznation of ganuna rays for single photon emission computed tomography. Also, the collamator 302 maybe used as an anti-scatoer and out of field of view radiation shield for positron emission tomography. The collimator along with the crystal housing radiation shield 303 and amplifier radiation shield housing 306 reduce the out of field events and allows focused coUection of ganum rarys within the desiired field of view. This aspect of the detector's construction and operation nray be useful for irr,aging specific sections of anatomy like the bteast and brain. Other anatomical portions of a body, e.g., the extremities, may also be ima.ged using the present detector and system. The pixilated scintillation crystal and opti.cal coupling 304 absorbs and bloclz the gamma rays and produces low levels of light photons proportional to the gamma rays' energy.

Pute9A ppliauiai [00$5] The light may be collimated or piped through crystal and optical coupling to the micro chanx-el plate amplifier 305. The miero channel plate amplifier 305 or equivalent position sensitive low level light amplifier coIlects the light fnam the pixilated crystal and optical coupling 304 and converts the light into electrons with a photo converter. The respective electrons are then amplified by several orders of magnicude and detected by independent detection channel anodes, nese anodes wiA have currents proportional to the energy, position, and time of the detected gamma ray. The respective two dimensional anode atray on the nnicro channel plate amplifier 305 or equivalent position sensitive low level lighL amplifiei are connectcd to the event processing channel cards 307.

100861 'Ihe event processing channel cards 307 amplify, integrate, and can detect the time of the respective pulse generated by detected gamma ray and perform channel independent analog to digital conveTsions. Also the event processing chazxnel cards 307 discriminate pulses for energy levels and generate accurate tirrung signals for coincidence detection. The event processing channel cards 307 are connected to the event processor backplane 308. The event processor backplane 308 may include several digital signal processors and micro processor to perform event digital event position, event energy, event time, and compress event data to be sent to frame processor.

[0087] It should be understood that the specific application at hand can detennine the specific constn3ction and arrangement of che present components of the above illustraave embodi.nient. For example, as to the softwware and/or hardware employed in the present systerm, the system designer can provide some or a11 of certain features within said software and/or hardware and/or finnware. Additionally, the layout of the components can incorporate some or all of the above functions and features into a single component or spread them among several discrete components. The ciro0its descnbed herein may be integrated onto one or more separate circuit boards, wafers, printed circuits, chips, application-specific integrated circuits ("ASICs") and the lilse.

Pao9Appliaztiac [008$] Referring to FIG. 31, the pi2cilated scintillation crystal and optical coupling 304 are shown with FIG. 31(a) showing a perspective and FIG. 31(b) showing a plan view of the same. 'Ihe array includes a plurality of scintillation crystals which may be pixelated or divided into a grid of discrete elements. The individual scintillation pixels 401 may be configured into a two dimensional ("2D") matrix forrnat or arrxy, for exampk along Cmesian (or x-y) coordinate dimensions. The scintillation pixels 401 are separated with septa rnateria1402. The septa materia1402 refkcts and assist in collimting the Ught to the exit end of the scintillation pixels 401.
At the end of scintillation pixels 401 an optical coupling maybe provided to transferthe light to the juxtaposed niicro channel plate amplifier 305 or equivalent position sensitive law kvel light amplifier.

[0089) FIG. 32 shows a micro chaninel plate amplifier 305 or equivaknt position sensitive low level light ampl.ifier with independent ehannel anodes 321. The micro channel plate arnmplifier 305 or equivalent position sensitive low lcvel light amplifier coIlecrs the light from the pixilated crystal and optical coupling 304 (see FIG. 30 and converts the light irno electrons wnch a photo converter. The respective electrons are then amplified by several orders of magnitude and detected by iudependent channel anodes 321. These anodes wil! have currents proportional to the energy, positian, and time of the detected gamma ray.''Ilae mspective two dimensional indepEndent channel anode 321 array on the micro channel plate amplifier 305 or equivalent position sensitive low level light amplifier arie connected to the event processing chuniel cards 307 (see FIG. 30 as mentioned previously.
[0090] FIG. 33 sho'ws some exemplary processing stages in an event processing channel card 307. The event processing channel cards 307 have independent channel event processor 331 (see FIG. 33). The independent channel event processors 331 are coupled to a matrix event processor 332 (see FIG. 33).

AatentApp+tutttia:
100911 FIG. 34 shows some maiun processing elements for an exemplary embodiment of an independent channel event processor 331. "I'he independent channel event processors 331 are connected to the two dimensional independexu channel anode 321 array on the micr+4 channel plate amplifier 305 (see FIG. 30 or equivalent position sensitive low level light amplifier. The independent channel event processors 331 consist of both analog and digital processing elemexrts. A channel preamplifier ("prearnp") 341 maybe coupled to the independent channel anode 321. 'I'he channel prearnp 341 amplifies the pulse signal and conditions it for event integrator 342 and pulse detection and trigger 343. An digital offsetlpulsa adjusrment is connected to the channel preamp 341 and event integrator 342 to provide canceling out of offsets to zero for event integrator 342. The event integrator 342 has an integrator reset 344 to allow for xndependent asynchronous pulse integrate reset cycles. The event integrator 342 is connected to the A/D converter 345 to perform analog to digital conversion of irnegrated pulse amplitude. The event process contro1346 controls the pulse detection and respective integrate, hold, reset cycle for digitizang of gamma raypulse. The pulse detection aad uigger 343 detects a pulse greater than a threshold and perform.s accurate timing detection of the pulse wirh respective differentiation or constant fraction discrimmation components.

[0092] FIG. 35 illustrates an exeniplaty matrpc event processor 332 (see also FIG. 33). The matrix event processor 332 is located event processor backplane 308 (see FIG.
30 and is coupled to a mukiple independent channel event processors 331. The matrix evern processor 332 allows event data acquisition and the resulting iurrage formation_ The event processor 332 inchides one or more digital process elements and/or nucro processors.

[0093] The processing performed by the event processor 332 includes processing perforrned by the trigger detection processor 351. The trigger detection processor 351 is coupled to a respective event process controIler 346 on a plurality of input channels.
'i'be trigger detection PatextAppltaxttQl processor 351 detects an event based upon a time variable or signal, and contmis which set of the pturality of channels is to perform the cornesponding event processing, signal ;ntegration, and analog-to-digital conversion. A 2D event channel selection element 352 determines which set of channels to sample for the event.

100941 An event "centroidA maybe defined for an event since the event maytrigger multiple channels and have enesgy distributed over moultiple charulels.
'Iherefore, a centra[ or typical or representative channel of a plura,lity of channels can be associated with an event as being most representative of that event. The event sample control 354 r.akes the centruid channels selected from the 2D event channel selection 352 and generates a synchronization timing sequence to run respective integration and analog-to-digital conversion cyeles on selected centrroid channels for the event. The timing and control signals frorn the 2D event channel selection 352 are sent the niultiple independent channel event processors 331 via a nlultiple channel cross point nn3hiplexer 353. The muhiple channel cross point multiplexer 353 bi-directionallytrazisfers respective control signals and data colleetion informacion to the plurality of channels on the indepen.dent channel event processor 331.

[0095] DUhen an event is detccted by the t,rigger detection 351, signals are sent to che time stamp interface 355 which is coupled through an interface to a common cirne stamp control process for generation and :etum of a tixne-of-event output for the event re]ative to other possible events in the system. The time stamp i.nterface 355 interacts with an exteraal time stamp processor and is used for coincidence detection of events.lhe time stamp interface 355 allows the event sample control sequence of sampling to be aborted if the event is not in coincidence with another event trigger on a 180 degree spatiatlropposed event channel.

[0096] I'he event position processor 356 uses information from each channel of the centroid of an event to deoennine the position of a source of a gamma ray detected bya respective PanmApplr,ratian pixel in pixilated scintillation cxystal and optical coupling 304 (see FIG.
31). The position is computed as a weighted center of gravity calculation for a closest pixel position determination. The event position, energy, and time are determined by the event position processor 356 and sent to the serial event input/output ("I/p") interface 357, [0097) The serial event I/O interface 357 is coupled to a framing processor for respective image fomiation and eventually generating a modality, e.g., SPE CI' or PET
image output.

[00981 The detector control process alloovs for cah%ration and general control of the muhi- (e.g., dual-) modality detection module 301 (see MG. 30, [0099] FIG. 36 illustrates another exemplary view of some main components of a dual rnodality detection module 361, The collimator 362, crystal housing radiation shield 363, and amplifier radiation shield housing 366 can reduce out of field of r-iew:adiation which could cause imaging errors. 'I1nse respective shields also provide control temperature envitroninent for the dual mvdality detection module 361.

[00100] FIG. 37 iIlustrates an exemplary system having the rnultr (e.g., dual-) modality detection modules 371 described above, having juxtaposed posiaons relative to one other so as to form an approxixnately curved dual modaliry detector array 374 with a substantially circular general profile (approximating a circle) about a certain region of interest ("ROI") 373. In some errkodiments, the ROI includes or consists of a space for irnaging a patient's organ or a diseased body part (e.g., brain, breast, arm, leg, etc.). It can be appreciated that, with collimators 302 in place, the individual detection modules 371 take on overlapping lines of sight covering the ROI 373, The dual modality detection modules 371 are connect via a base plate 372 and can be translated and oscillated as a unit. The base plate provides structural support to fix the detection modules 371 thereto to provide a common spatial frame of reference. In some embodiments, the individual detection modules 371 are rigidly fixed to the support base plate 371 and therefore the individual PaontApp&xtirn detection modules 371 w+e sparially fixed relative to one another. The base support plate 371 can be rotated as a whole and the detection modules 371 ateached to the support plate 372 will rotate along with it and therefore be moveable with respect to a patient, organ, ROI, patient support platform, organ support stnutuir, or the L1se. This allows imaging with the muhiple modes of imaging empbyed from a variety of directions as needed. Note that other degrees of freedom, such as swiveling, tilting, vibrating, spinaing, spira.l movement, and the like are available in addition to the rotation described above to allow a better or substantially full spatial coverage of the ROI 373 in use for generating the tomographic images. An arciculated elemcnt can be used to couple said structural support frame of the imaging apparatus to the detector elemerux so that they can move along said degrees of fneedom. Joints, hinges, motors, lead screws, ball-bearings and other mechanical and electromechanical elements can be used to anieulate said movement.

1001011 FIG. 38 iffiistrates a pair of exemplary curved dual modality detector arrays 380 positioned 180 degrees with respect to one another to form a positron en~ssion tomography imaging apparatus according to an excmplary ensbodiment. Ene:gy from 511 KeV
garrnna rays from a positron annihilation event, traveling along line 383 in opposing directions, can be detected by the pair of opposing detectozs 381 and 382. The curved detector arrays 380 can themselves be rotated about a central axial axis, translated radially, tilted outside a plane of their curvature (outside a plane normal to the central axial axis), or oscillated about any given axis to achieve a mone complete image coverage according to principles of superposition and tomographie imaging.
Additionally, the individual detector modules may be rotated, translated, tilted, and osciilated about one or mone axes in one or more degx+ees of freedonL Nbtorized apparauu and actuators can be used to accomplish the motions described above.

[00102] Enmbodiinents of the present systems and rnethods include a multi-modality tomographic modular iurraaging detector comprising at least one 2D pixelated scintillation crystal PatemApptid~
array, a geometric optical coupling, a compact micro channel amplifier plate with a 2D matrix of independent anode charme]s, an independent channel event processing for each of the anodes, a 2D
matra event processor for gauuna rays spatial, energy, and tune of detection.

[00103] The mu}tif-modalitytomographic specific modular itnaging der.ector may furtber include means for deterrn+=+, g a super-resolution with a phualicyof pixels per anode channel, or with adaptive weighted position detection.

[00104] 'I'he muhi-rmodalitytomographic specific modular imaging detector can further include means for coincidence imaging with two more modnles to perfoim positrvn emission tomographic itnaging.

[00I05] The multi-modalitytomographic specific mdular imaging detector modules may be further cascaded into a mosaic of subscantially curved detector arraps for single photon emission computed tomographic imaging.

[00106] 'lhe mukimmwdaGtytomographic specific modular imaging detector maybe further cascaded ;uto a mosaic for dual curved detector arrays to perfornx positron emission t.omogmphy.
[00107] The muletmodalitytomographic specific modular imaging deteccor maybe furdher coupled to amspeetive mechanical collirnators for single photon ennission tomography.

[00108] The mulc~modality tomographic specific modular irnaging deieetor may be further coupled to mechanical anti scatter baffle colliimtois for positron emission tomography, [00109] The multi-modalitytomographic specific modular imaging detector maybe further coupled to coincidence detection and 21) image histogram processing modules for image generation.
[001101 The muhi-modality tomographic specific modular iunaging detector may include a plurality of translatable and rotatable detector units to perform super resolution single photon emission tomography.

P44entApP&3tian 1001111 The m-ilci-modaktonnographic specific modular imaging detector can be designed to be cransLuble and rotmble to perform super resolution positron em,ission tomography.
1001121 Accord.ingly, at [east two imaging modalities (e.g., X-ray and PET; X-ray and SPECT; CI'; and others) can be employed to detect a coxnmon condition. The imaging apparatus and method can be employed to fuse together or combine the outputs of said detection rnodalid.es into a single useful output.

1001131 In some embodiments, the multi-modal detection comprises a first imaging modality (e.g., PET or SPECI) for detecting a functional aspect of a subject or oagan while a second iznaging modality (e.g., X ray) is used for detecting an a.natomical aspect of a subject or organ.

[00114] The appazatus descrlbed above allows, in some embodiments, dua~ or multi-modality imaging of a patient without irquiring the patuent to move from a fiust position to a second position corresponding to the two imaging modalities used. As opposed to some systems presently in use that require moving the patient or translating the gurney on which the patient is placed from a first rnodaGty imager to a second modality irnager, here, the patient can be imaged using more than one modality coupled to a conunon frazneworic while the patient remains substantially stationary.
This can impror-e the clarity, resolution, and accuracy of the multtmodal image, and provide greater comfort and saferyto the paticnt.

[00115] In other embodiments hereof, imaging an organ can be conducted without rrequiiing physical or nlechaniccal contact between the organ and the imaging apparatus. For example, nnblce present imaging systems that often require awoman's breast to be cornacted or deformed or pressed by an uncomfortable imaging device, the present system allows a no- contact imaging of the breasc, especially if presented within a region of interest within the present curved azray detector system.

PutezAppfrattian [00116] As discussed above, thcsc components and processors can be implemented in software, ha:dware, firmware, or various combinations thereof, and the present illustrative demancation of the funccions and block diagrams and components described can, be accomplished flexibly in more than one way. For example, one or more additional components may be incorporated into the present system, or a single component can be constructed to perfonrn the functions of twu or more compon.ents described in the present preferred ennbodiments.

J001171 The present disclosure is not intended to be limxted by its preferred embodiments, and other embodiments are also comprehended and within its scope. Numernus other embodiments, modifications and extensions to the present disclosure are nnended to be covered by the scope of the present inventions as claimed belaw. This includes implementation details and features that would be apparent to those skilled in the an in the mecba-ical, logical or electmnic implementation of the systems described herein.

1001181 DVlaat is claimed is:

Claims (22)

1. A medical imaging apparatus, comprising:
a first detector contributing a first imaging modality for detecting a medical condition in a region of interest;
a second detector contributing a second imaging modality for detecting said medical condition in said region of interest, said second imaging modality being different than said first imaging modality, and a structural frame supporting both of said first and second detectors, said frame providing a common mounting point for supporting said detectors and positioning said detectors in a configuration supporting imaging of said region of interest.

2. The apparatus of claim 1, said first detector comprising a photon detector.

3. The apparatus of claim 1, said structural frame allowing imaging a patient using both of said first and second imaging modalities without requiring an intervening movement of a subject being imaged.

4. The apparatus of claim 1, said structural frame being coupled to said detectors with articulated elements for permitting a movement of said detectors along at least one degree of freedom.

5. The apparatus of claim 1, said first detector comprises an anatomical detector, and said second detector comprises a functional detector.

6. The apparatus of claim 1, said first and second imaging modalities comprising respective outputs combinable to form a fused multi-modal output of said apparatus for detection of said medical condition.

7. The apparatus of claim 1, said first and second detectors including first and second respective collimators disposed at respective input ends of said first and second detectors to collimate a respective input to said first and second detectors.

8. The apparatus of claim 7, said collimators comprising a plurality of longitudinal channels disposed substantially parallel to one another within a shielding matrix, said longitudinal channels permitting passage of a respective input to a corresponding detector and said shielding matrix comprising a material that substantially prevents passage of said respective inputs to said corresponding detector.

9. The apparatus of claim 1, further comprising a mechanical anti-scatter baffle collimator for collimating an input to said detectors.

10. The apparatus of claim 1, further comprising a plurality of independent channels for capturing a respective plurality of signals responsive to a detected event.

11. The apparatus of claim 1, further comprising a coincidence detection apparatus for determining an event.

12. A method for generating a multi- modal image for detecting a medical condition, comprising:
imaging a region of interest using a first detector having first imaging modality for detecting said condition;
imaging said region of interest using a second detector having second imaging modality for detecting said condition;
coupling said respective detectors to a structural support frame so as to support said detectors and position said detectors in a configuration allowing imaging of said region of interest;
and combining respective outputs of said first and second detectors so as to form a multi-modal combined output thereof indicative of said condition,

13. The method of claim 12, where imaging with said first imaging modality comprises detecting a photon.

14. The method of claim 12, where imaging with said second modality comprises detecting a charged particle.

15. The method of claim 12, where imaging with said first and second modalities comprises detecting a photon and a charged particle, respectively.

16. The method of claim 12, further comprising correction of an attribute of said combined output.

17. The method of claim 12, further comprising calibrating said first and second imaging modalities.

18. The method of claim 12, further comprising placing an array of said first imaging modality detectors and said second imaging modality detectors along a substantially curved profile for the purpose of imaging a region of interest containing an organ.

19. The method of claim 12, further comprising placing a selected subset of a patient's body so that a selected organ lies within a region of interest generally defined by said first and second imaging modality detectors.

20. The method of claim 12, further providing said combined output to a program for generating a viewable image including information collected from said fust and second imaging modalities and indicative of said condition.

21. The method of claim 12, further comprising placing a female human patient upon a support surface including at least one opening through which at least one breast may be imaged using said first and second imaging modalities.

22. The method of claim 12, further comprising receiving a plurality of independent channel signals corresponding to respective outputs of respective pixelated scintillation crystals of said first and second imaging modalities, and determining a position of an event based thereon.