1Bi

INTRchallespecidefichaveIn thwe th

THEDRAstransdata formin Fig(a) vein to strea(a)).

METhealt(Magcoil agap) (prodanglecalibradiadelayAlthothe rPE re

RESrecon(a,b) CartesameLV/eaarrowintenseen showintenwherare freduc

DISCalongGibbprojestresis notREFEet al.,et al.

ProjBehzad Sharif1, R

omedical Imaging

RODUCTIONenging dynamicifically the so-ca

cits [1-3], and are been many atteis work, we demherefore propos

EORY In Cartess due to an inhsitions [3,4]. Hotransform is the as FT (instead s

g. 1 using a numersus 108 projecthe blood-pool/

aking artifacts in

THODS To invthy human volgnetom Verio, Siarray. Two first-using a single-s

duct) sequence e = 12; TR/TE = rating parallel im

al) with 36-40 rey correction anough the readouradial scheme (≈esol. ≈2.6 mm) a

SULTS Fnstruction resul

and human (cesian/radial imae phase of thearly-myocardial ws in panels (ansities that were

in the figure,w DRAs (arrownsities) in the reas the projectfree of dark rimced contrast-to-

CUSSION Reg the PE directios ringing, a maj

ection imaging (s imaging. Howet sufficient and cERENCES [1] W, JCMR 2009;11(17MRM 2006;55:11

jection ImaginRohan Dharmakumg Research Institut

N Despite signific imaging applicalled subendocae especially limitempts at minimimonstrate that pse radial k-space

sian MP MR, Giherent property

owever, in projee Radon transforshows streaking

merical phantomctions in Panel (b/myocardium bon (b) do not resu

vestigate the valunteers (N=4; iemens AG Healtpass MP scans hot radial (custo(common param2.4/1.4 ms; TI

maging (TGRAPPeadouts. The cu

nd a 4-fold inteut resolution for≈1.8 mm vs. ≈2.2nd radial scans (

igure 2 shots for representc,d) scans. Eacages correspone contrast upta

enhancemen) and (c) point e considered DR, Cartesian imaws pointing t

subendocardiation reconstruct

ms (although wit-noise ratio).

cently, a major aon) and thereby or contributing radial trajectoriever, to match tconstrained (e.gilke NM, et al., JM

7). [5] Kak and Slan50-6. [8] Plein S, e

ng of Myocardmar1, Chrisandra Se, Cedars-Sinai M

Institute, Cedars

cant technical aations [1,2]. Curdial dark-rim ating since they czing DRAs in spe

projection imagi sampling as a p

bbs ringing alony of the Fourieection imaging (rm [5], which doartifacts if high

m simulation withb)). Fig. 1(c) showorder. It can be sult in a “signal d

idity of this obsIRB approved)

thcare, Erlangen(SR-prepared FLomized) pulse semeters: FOV rea= 100 ms). Bot

PA for Cartesian ustomized radiaerleaving schemr the Cartesian s2 mm), the over(isotropic ≈2.2 m

ows the tative dog h pair of d to the ake (late-nt). The

to hypo-RAs. As is ages (a,c) to hypo-l regions

tions (b,d) th slightly

approach for elireducing Gibbsfactor to DRAs.es). The presenhe high resoluti

g., using compresMRI 1999;10:676-68

ney, Principles of Cet al., MRM 2007;5

FhecoenD

dial PerfusionShufelt2, Troy LaB

Medical Center, ands-Sinai Medical C

advances over trrent clinical Mrtifact (DRA) [2-can reduce the secific protocols, ing of first-pass

preferred acquisi

ng the phase-ener transform (FT(radial k-space

oes not exhibit thly undersampledh realistic intensws a 1D cut alonseen that, unlikedip” (which caus

servation in-vivo were imaged

n, Germany) witLASH) were perfequence followead = 270-300 mh scans were acand self-calibratl sequence inco

me combined wscan was higher rall resolution o

mm in-plane) we

minating the DR ringing [8,9]. In We conclude ted results wereons achieved in ssed sensing) pr85. [2] Gerber BL, Computerized Tom58:777-85. [9] Ota

igure 2. Repreealthy canine morresponds to nhancement pha

DRAs are not see

n: Minimizing ounty2, Louise Thd University of Ca

Center, Los Angeles

he past decadeP MR methods 4]. DRAs are cau

sensitivity/specifyet it remains amyocardial perfition scheme for

code (PE) directT) at sharp signacquisition), thehe Gibbs ringingd). This fact is desity values (108 ng the PE directie the Gibbs ringises noticeable D

o, healthy canineon a clinical

h a 32 channel cformed at rest (ed by a single-shmm; BW ≈ 800 ccelerated usingting non-Cartesi

orporated adaptwith KWIC proc

than the base rof Cartesian (anisere matched to w

RAs in first-pass n this work, we that an alternate limited to restadvanced Carte

rojection reconstet al., JCMR 2008

mographic Imagingzo R, et al., MRM

esentative in-vivomodel; (c,d) hea

the same phaase). The arrow

en in the projectio

the Subendochomson2, Noel Baialifornia Los Anges, California, Unit

e, myocardial pesuffer from imaused by multipleficity of detectin

an active area offusion is robust r DRA-free perfu

tion leads to nal intensity e underlying g in the same emonstrated PEs in Panel on, zoomed-ng in (a), the

DRA in Panel

es (N=3) and 3T scanner

cardiac-torso (>10 minutes hot Cartesian Hz/pixel; flip g rate 2 self-ian SENSE for tive gradient-cessing [6,7]. resolution for sotropic with

within 10%.

MP MR has beedemonstrated ttive strategy (bet scans, althoug

esian schemes (etruction will be

8, 10(18). [3] DiBelg, IEEE, 1988. [6] S2010; 64:767-76.

o results for reslthy human volu

ase of the cows in (a) and (c) on-reconstruction

cardial Dark-Rirey Merz2, Danieleles, Los Angeles, Cted States

erfusion (MP) Mage artifacts thae factors and mng subendocardf ongoing resear

to Gibbs ringinusion imaging.

en to improve ththat projection iesides increasingh we expect the.g., [8,9]), rate needed. la EV, et al., MRM

Song HK, et al., MR

st first-pass myounteer. Each pantrast uptake point to dark-ri

n (radially sample

Figure 1. Numintensity valuesprojection imaCartesian imagas highlighted108 projectionreconstruction present). (c) a zoomed-in to b

Rim Artifact S. Berman2, and DCalifornia, United

MR imaging is onat reduce diagn

mimic subendocaial MP deficits. Rch ([2] and referg, a major cause

he spatial resolumaging is inhereg the resolution

he same propert2 parallel imagin

M 2005;54:1295-59RM 2000;44:825-3

ocardial perfusionair of Cartesian/(late-LV or eam artifacts (DRAed) images in (b

merical simulatios) demonstratingaging to Gibbging with 108 PE); (b) projection

ns and filtered (mild streaking1D cut along th

blood-pool/myoca

Debiao Li1 d States, 2Heart

ne of the most ostic accuracy,

ardial perfusion Recently, there rences therein). e of DRAs; and

tion (especially ently robust to n) is to employ ties to hold for ng acceleration

9. [4] Ferreira P, 32. [7] Peters DC,

n scans: (a,b) /radial images

arly-myocardial As). However, ) and (d).

on (with realistic g robustness of s ringing. (a)

Es (DRA is seen n imaging with

backprojection g artifacts are he PE direction, ardium border.

1144Proc. Intl. Soc. Mag. Reson. Med. 20 (2012)