Charlie Yi Wang1, Yuchi Liu1, Shuying Huang1, Mark Alan Griswold1,2, and Xin Yu1,2
1Biomedical Engineering, Case Western Reserve University, Cleveland, OH, United States, 2Radiology, Case Western Reserve University, Cleveland, OH, United States
Synopsis
We propose a novel 31P Creatine Kinase encoding Magnetic Resonance Fingerprinting method
(CK-MRF) to efficiently measure high energy phosphate metabolism through
creatine kinase (CK). Measurement reproducibility of CK rate constant (kf,CK)
using CK-MRF was compared with both conventional 31P saturation transfer
method, and Four Angle Saturation Transfer method in rat hind limb. CK-MRF measurement showed comparable or
superior reproducibility using 20 s experiment time compared to 160 s experiment
time of either comparison method.
Changes in kf,CK following Ischemia/Reperfusion (IR) were
also measured. Background/Purpose
31P Magnetization
Transfer spectroscopy (MT-MRS) has been used to measure high energy phosphate
metabolism via creatine kinase (CK)
in
vivo. However, current
31P
MT-MRS methods require prohibitively long experiment time, which limits their clinical applications. In this study, we
propose a novel Magnetic Resonance Fingerprinting
1 (MRF) framework based method, the Creatine Kinase encoding MRF method (CK-MRF), to increase
measurement efficiency of
31P metabolism through CK. Measurement
accuracy and reproducibility of the creatine kinase forward rate constant (k
f,CK) using
CK-MRF was compared with conventional methods in rat hind limb. Changes in k
f,CK following Ischemia/Reperfusion
(IR) were also measured.
Methods
CK-MRF
acquisition consisted of an inversion preparation pulse followed by 320
acquisitions arranged in blocks, alternating between phosphocreatine (PCr) and γATP excitation
(Fig. 1). The acquisition was organized
into two sections, composed of blocks of 10 ramped excitations with 12.8 ms TR. Excitation flip angle (FA) in both sections
was modulated by a sinusoidal envelope. Following
each excitation block, frequency selective saturation was achieved with a 470 ms
BISTRO scheme. Saturation frequency at either
2.4 ppm upfield of PCr (γATP saturation, section 2) or 2.4 ppm downfield of PCr
(control saturation, section 1) was used.
Total acquisition time for 1 fingerprint average was 20 s. RF excitations used Gaussian shaped
spectrally selective pulses (4 ms duration) with alternated phase. FID signals were acquired in a 7.8 ms window
with 30 ms
dwell time. Signal evolutions for both
PCr and γATP
were extracted by Fourier transform.
A dictionary
was constructed using Matlab-based Bloch-McConnell simulator that included four
matching parameters: intrinsic PCr longitudinal relaxation time (T1,PCr),
pseudo-first order CK exchange rate (kf,CK), PCr to ATP ratio (M0,PCr/M0,γATP),
and PCr chemical shift (δPCr). Dictionary resolution for T1,PCr,
M0,PCr/M0,γATP, and δPCr was 0.25 s, 0.3,
and 6.25 Hz respectively. kf,CK
used an adaptive resolution of 0.006 s-1 and 0.03 s-1 for
values below and above 0.415 s-1 respectively. The dictionary totaled 132,660 entries.
Animal
studies (n=3) were performed on rat hind-limb at 9.4T using a custom-built 31P
saddle coil. An inflatable cuff was
placed at the thigh of the rat to induce ischemia. During baseline, 3 methods were compared for
measurement precision: CK-MRF, conventional MT by 31P saturation
transfer2, and Four Angle Saturation Transfer3
(FAST). A total of 1800 s of data was acquired
for each method. Acquired data was retrospectively
averaged without view-sharing and the results of parameter
estimation with different number of averages were compared.
Following
baseline data acquisition, 20 min ischemia was induced by inflating the cuff to
300 mmHg followed by 10 minutes of reperfusion for stabilization. Afterwards, CK-MRF and conventional 31P
saturation transfer were acquired in interleaved fashion for a total of 20 min
each.
Results
Figs.
2a&b show representative fingerprints acquired
in vivo. Fig. 3 shows the measurement
accuracy and reproducibility of baseline k
f,CK for all 3 methods using
different number of signal averages, corresponding to an acquisition time of 20
s (CK-MRF and FAST methods only), 160 s, 320 s, and 1800 s, respectively. Even with 20 s acquisition (single average), CK-MRF
demonstrated similar or better precision compared to 160 s signal averages of either
conventional MT or FAST acquisition. Data
from 20 s FAST acquisition yielded nonsensical data. Both CK-MRF and conventional MT detected an
increase in post-ischemia k
f,CK. CK-MRF observed an increase from
0.315 s
-1 at baseline to 0.349 s
-1 after reperfusion, while conventional
31P saturation transfer observed an increase from 0.338 to 0.374 s
-1.
Discussion/Conclusion
In
this study, we present the use of a spectroscopic MRF method to increase the
sensitivity to creatine kinase activity.
The current iteration shows good agreement with conventional
31P MT measurement methods
with far superior measurement efficiency leading to the possibility of
performing spatial mapping measurements.
Acknowledgements
The authors would like to acknowledge funding from NIH TL1-TR000441, T32-EB007509,
F30-HL124894, R01-HL73315, R21-HL126215.References
1. Ma, D. et al.,
Nature 2013;495:187–92.
2. Xiong, Q. et al., Circulation Research 2011;108:653–663.
3. Bottomley, P. et
al., Mag. Reson. in Med. 2002;47:850–863.