Trial Information

Multiple myeloma (MM) is a clonal plasma cell neoplasm characterized by proliferation of
abnormal plasma cells in bone marrow (BM) that secrete a monoclonal paraprotein (M-protein)
in serum and/or urine, and by osteolytic bone destructions. So far, it is an incurable
disease and its pathogenesis is largely unknown. The median survival time of MM patients is
only three to four years, and then the patients will die on either the disease or its
complications [Barlogie et al, 2004].

There are several independent prognostic factors for MM, like high levels of beta-2
microglobulin, hypodiploidy chromosome content, deletion of chromosome 13q14 and also the
extent of angiogenesis, shown by microvascular density (MVD), in BM [Fonseca et al, 2004;
Kumar et al, 2002; Pruneri et al, 2002; Sezer et al, 2000]. It has been suggested that MM
progressed from an avascular to a vascular phase (active MM) accompanied by a significant
increase in MVD in BM [Rajkumar et al, 2002], which is promoted by the angiogenesis related
factors, like VEGF, bFGF, and PDGF, which were performed like a paracrine or autocrine loops
secreted by MM cells per se or the adjacent BM stromal cells [Gupta et al, 2001; Kumar et
al, 2003; Ria et al, 2003; Vacca et al, 2003]. It has been reported that higher MVD in BM at
the time of initial diagnosis was associated with shorter OS and PFS in patients undergoing
autologous transplantation for MM than the patients with lower MVD [Kumar et al, 2004].
Those angiogenesis related factors may provide disease monitoring but also a potent novel
therapeutic approach to over come resistance to therapies and thereby improve patient
outcome [Podar et al, 2004]. Interestingly, the patients with deletion of chromosome 13q14
have higher MVD in BM than the patients without [Schreiber 2000], which hinted that the
grave prognosis of deletion of chromosome 13q14 might be a result of dysregulation of
angiogenesis in BM. However, on the other hand, absence of clinical prognostic value of VEGF
and MVD in MM had also been reported by other investigators [Ahn et al, 2001; Choi et al,
2002]. In MM, whether the MVD in BM and the related biological markers, like VEGF, bFGF, and
PDGF can serve as prognostic factors are still debate [Rajkumar et al, 2001; Vacca et al,
2001]. There are possible two reasons for the debate, the first one is that the distribution
of neoplastic foci within the BM of MM are not homogenous, therefore the microvascular
densities calculated from a single site BM specimen are hard to represent the total
angiogenesis within the BM; the second one is that the angiogenesis related biological
markers, such as VEGF, bFGF, and PDGF, in MM are largely studied on the plasmas obtained
from peripheral blood rather than BM, and this is a critical issue for the cytokines
secreted from either MM cells or adjacent stromal cells are mostly paracrines or autocrines
and the levels of VEGF, bFGF, PDGF are higher in BM than in peripheral blood [Di Raimondo et
al, 2000].

Reviewing the literature, dynamic contrast-enhanced MRI has been used to evaluate the
potential of vertebral fractures in MM [Scherer et al, 2002a & 2002b], to quantify
significant changes of BM microcirculation during conventional treatment [Rahmouni et al,
1993] or treatment with thalidomide combined with chemotherapy [Wasser et al, 2004], which
may be a novel and non-invasive tool to approach the clinical outcomes of MM patients
[Moehler et al, 2001]. In short, MR imaging of the spine was performed with a 1.5-T
superconducting system (Magnetom Vision Plus; Siemens, Erlangen, Germany). A phase-array
spine-coil was used, and a routine fast spin-echo T1-weighted sequence (repletion time
msec/echo time msec, 600/12; turbo factor of three; section thickness, 4 mm; field of view,
28cm) was performed in the midsagittal plane and covered the area from T11 through the
sacrum. A dynamic contrast-enhanced MR study was then performed (section thickness, 10 mm;
field of view, 28 cm) at the midsection of the vertebral body and covered the same area. The
pulse sequence used was a turbo fast low-grade shot gradient-echo sequence (8.5/4.0;
prepulse inversion time, 160 msec; flip angle, 10°; acquisition matrix, 72x128). Acquisition
time was 0.89 second with 0.11-second delay. In total, 100 dynamic images were obtained
within 100 seconds (one frame per second) in each subject. After the initial 100-second
scanning, the scanning were prolong to 600 seconds with the scan rate 1 frame per 10 seconds
(1 seconds scan and 9 seconds delay). An injection of 0.1 mmol per kilogram of body weight
gadopentetate dimeglumine (Magnevist; Schering, Berlin, Germany) was administrated by the
power injector through a 21-gauge intravenous catheter that was inserted in the right
antecubital vein previously. A brief constant injection rate of 2.0ml/sec were used. This
injection was immediately followed with a 20-ml saline flush at the same injection rate.
Dynamic imaging started when the injection of the contrast material commenced.

Signal intensity values were measured in an operator-defined region of interests (ROIs). The
musculoskeletal radiologist (T.T.F.S., with 15 years experience) places the ROIs were placed
with the aid of a cursor and a graphic display device, along the border of
high-signal-intensity bone marrow on T1 weighted images covered the entire bone marrow of
each vertebra. One vertebral body was covered by one ROI measurement. The ROI was measured
separately for each of selected lumbar vertebrae (L2, L3 and L4) in each subject. The signal
intensity values derived from the ROI measured in each vertebral body were then plotted
against time to obtain a time–signal intensity curve (Fig 1) for each vertebral body. The
baseline value for signal intensity (SIbase) on a time– signal intensity curve was defined
as the mean signal intensity from the first three images. The maximum signal intensity
(SImax) was defined as the maximum value of the first rapidly rising part of the time–signal
intensity curve. The time to peak contrast enhancement was defined as the time (Trise)
between SIbase and SImax. After the peak, which usually occurred about 40 seconds after the
start of injection, the time–signal intensity curve entered an equilibrium phase that lasted
about 30 seconds. The total 100-second imaging time encompassed both the first rapid rise in
the curve and the early equilibrium phase. In our study, the SIbase and SImax were measured
only from the first rapidly rising curve. For the semiquantitative analysis, the peak
enhancement ratio peak was calculated for each ROI as (SImax – SIbase)/SIbase and average
enhancement slope (average slope) was defined as (SImax – SIbase)/ Trise for each ROI. The
initial slope was measured as the most steep uprising slope from the early rapid-rising part
of time intensity curve. The mean value was calculated from the parameters of the L3, L3 and
L4 vertebrae and represented for each subject. In our preliminary study, like others
[Moehler et al, 2001], this constructed images performed by dynamic contrast-enhanced MRI,
which mimic the perfusion status within bone marrow, had been correlated with distinct
clinical outcomes in our acute myeloid leukemia and MM patients in a preliminary study.

Accordingly, we would like to have the BM perfusion status imaged by dynamic MRI to mimic
the macroscopic vascular densities of BM, and thereafter, the BM perfusion status, the
clinical outcome of the MM patients, and the angiogenesis related biological markers will be
correlated.