Figure 1.Illustration of the harmonised multiparametric renal MRI protocol

Table 1. The detailed parameters of harmonised multiparametric renal protocols

Figure 1: A) Longitudinal relaxation time (T₁) for the CKD cohort at baseline divided into ‘stable’ (n=13) and ‘progressors’ (n=9), B) Percentage change in T₁ at Year 1 and Year 2 as compared to baseline for the ‘stable’ and ‘progressor’ group, C) Individual subjects shown at baseline, Year 1 and Year 2 with the ‘stable’ group shown in black and ‘progressors’ in red. [CM diff = corticomedulllary difference]

Figure 2: A) Renal cortex perfusion for the CKD cohort at baseline divided into ‘stable’ (n=13) and ‘progressors’ (n=9), B) Percentage change in perfusion at Year 1 and Year 2 as compared to baseline for the ‘stable’ and ‘progressor’ group. C) Individual subjects shown at baseline, Year 1 and Year 2 with the ‘stable’ group shown in black and ‘progressors’ in red.

Figure 3: Diffusion weighted imaging (DWI) ADC values in control participants and patients with CKD. (Top panel) ADC maps of a control and (failing renal transplant) patient. (Bottom panel). ADC values were significantly lower in patients compared to healthy controls for whole kidney, cortex and medulla.

Figure 4: T1 MOLLI relaxation times in controls and patients with CKD. (Top panel) T1 maps of a control and (failing renal transplant) patient. (Bottom panel). T1 relaxation times were significantly greater in patients compared to healthy controls for whole kidney and cortex, whereas no significant difference was observed in the medulla between the two groups.

Figure 4. Case examples of renal blood flow maps in persons A) with SSBP and B) non-SSBP. Cortical renal blood flow maps (ml blood/100 g tissue/min) are shown from the 4x acquisition protocol. The subject with SSBP exhibits lower cortical perfusion compared to the non-SSBP subject, consistent with group trends. The color bar and range of values for renal blood flow are shown top-right using a perceptually uniform colormap (magma)⁷.

Figure 3. Renal blood flow (RBF) in groups with SSBP and non-SSBP. Salt sensitive blood pressure (SSBP) and non-SSBP groups were compared for cortical RBF, that demonstrated a trend towards reduced cortical RBF in SSBP (174.5 ± 53.9 mL/100g/min) compared to non-SSBP (253.8 ± 111.7 mL/100g/min) groups (p=0.07). This box plot demonstrates the median as the central line, and upper and lower quartiles as the edges of the boxes.

Fig 3. A: Pearson correlation matrix (absolute values) of MRI, hydroxyproline, histology, serum biomarkers, and gene expression data. High correlations are in red and low correlations are in blue. B: Schemaball for all metrics. Curves are colored by correlation between two metrics (magenta = negative correlations and yellow = positive correlations). Green nodes represent cumulative correlation between the individual metric and all other metrics. Control n=5 and oxalate n=8 for all data points except for gene expression (control n=5, oxalate n=4).

Fig. 1. Images of control and oxalate fed mouse kidneys. T₂-weighted, axial diffusivity, and fractional anisotropy of control (A) and oxalate kidneys (B). Collagen III histology of control (C) and oxalate kidneys (D). Collagen I histology of control (E) and oxalate kidneys (F). Histology insert images are shown at 5× magnification. Control n=5 and oxalate n=8. Scalebar = 2mm.

Figure 2: Comparison of axial vs coronal slice orientation and its effect on the tumor volume estimation (A). Representative T₂-weighted axial and coronal images (B). Comparison of 1 mm vs 0.5 mm slice thickness and its effect on the tumor volume estimation (C). Representative T₂-weighted 1mm and 0.5 mm slice thickness images (D).

Figure 3: Lesion volume change with respect to baseline in control and treated mice (A). Mean ADC changes in control and treated mice over time (B). Representative ADC maps overlaid on diffusion weighted imaged at b = 25 s/mm² at baseline and week 3 for control and treated tumors (C).

Fig. 1: Kidney images with short (left, 25 ms) and long (right, 60 ms) TE of one exemplary animal, showing fine detail, sharp boundaries and good cyst to tissue contrast

Fig. 2: Automatically detected cysts from one exemplary animal (left), histogram of cyst size and total volume of every cyst size (right)

Figure 1: Example ADCT, ADCD, FA, and FP parameter maps a) derived from a PACE-triggered and (b) derived from a respiratory-triggered DTI scan of a volunteer.

Table 3: Mean ± SD of the DTI parameters obtained from the three different sequence variants and comparison between medulla and cortex.

Table 1: The performance measures of Mask R-CNN for segmentation of kidney using 2D T2w images.

Fig. 1. The bar plot demonstrates the total number of slices in which Dice and IoU scores ranged from 0 to 1.

Figure 1. (a) A Cartesian grid of a ky-kz space showing CASPR view ordering, where the earlier echoes are acquired at the beginning of each echo train (blue dots) following a pseudo-spiral trajectory towards the later echoes (red). (b) VD-CASPR method acquires profiles in region 1 (R1, open circle), 2 (R2, asteroid) and R3 (dot) with variable density (e.g. 3, 2, and 1 averages respectively), but still maintaining a spiral profile ordering on a Cartesian grid for each echo train.

Figure 2. Kidney perfusion weighted images of a normal volunteer acquired using single-average 3D TSE-CASPR (a, top row) and with VD-CASPR method (b, bottom row), shown for several slices of the kidneys. VD-CASPR images showed minimized background noise and improved SNR. Note some signal variation between the right and left kidneys, probably due to B1 inhomogeneities.

Fig. 1: K^trans (s^-1) maps of the cortical region overlaid on the left kidney of a mouse. The raw AIF was used to compute the K^trans maps using the non-linear Tofts (a), extended Tofts (b), and the SSM (c).

Fig. 2: Boxplot of mean K^trans (s^-1)values from fitting of nonlinear Tofts, extended Tofts and SSM using AIF derived from (a) raw data, (b) SSA denoising, and (c) bi-exponential fitting.

Mono-exponential ADC and IVIM-related parameters (D, D*) measured in the renal cortex (top row), renal medulla (middle row) and skeletal muscle (bottom row).

Perfusion fraction f_p obtained from the IVIM analysis in the renal cortex (top row), medulla (middle row), and skeletal muscle (bottom row).

Figure 1: Typical voxel position in axial, coronal and sagittal planes. A small water-containing bottle (circled) was attached to the centre of the coil as a marker of coil position.

Figure 2: 31P spectrum of the normal human kidney in situ. (a) The added spectrum of the five healthy volunteers, (b) fitted spectrum, (c) individual components, and (d) residue.

Figure 3. Box plots for T₁, T₂* mapping in the renal cortex and medulla (ROIs), arterial RBF (BSA normalised) using PC-MRI, and renal perfusion (ml/min/100ml) with ASL, from 4 repeatability measurements in 5 healthy volunteers (HV) on the reference MRI scanner (MAGNETOM Prisma 3T, Siemens Healthcare GmbH, Erlangen, Germany) using the iBEAt MRI protocol. Pairwise comparison using t-test shows the statistical significance of differences (ns: not significant = p > 0.05; *p ≤ 0.05; **p ≤ 0.01; ***p ≤ 0.001) between HVs.

Table 1. 95% confidence interval for the mean value of each parameter (1^st column), and for the mean value of their RE (2^nd column) and RRE (3^rd column). Literature values of RRE (4^th column).

Figure 1: The 7 compartment model; F_med=E_VR,PAF_cor . A aorta; V renal veins; PV venous plasma compartment (low pressure vascular spaces including veins and peritubular capillaries); PA arterial plasma compartment (high pressure vascular spaces including arteries and glomeruli); PT proximal tubules; DT distal tubules; VR vasa recta; LH loop of Henle; CD collecting ducts; U urine. The blue arrows represent reabsorption flows carrying mainly water but no contrast agent.

Figure 3: Example of a and b) a 7CM fit to simulated data and c and d) a 7CM fit to patient data (only the first 300 s are shown). Note that the model fits the first pass peak well in simulated data, while it is not capable to capture the full height of the first pass peak in patient data. The oscillations on the AIF are due to inflow effects.

Figure 4. In vivo Z-spectra of cortex (a), medulla (b) and calyx (c) in one rat kidney after intravenous injection of iodixanol and iobitridol mixture, and the fitting results using the multi-pools Lorentzian model .

Figure 5. Resolved maps of two CEST effects at 4.3 ppm (a) and 5.5 ppm (b) obtained from acquired Z-spectra of one rat kidney under a saturation power of 1.5 μT; Ratiometric image (c) and the pH map (d) obtained from the two CEST effects.

Figure 1. (a) Supine and (b) upright positions in the multiposture MRI. Regions of interest (yellow open circles) on the (c) velocity, (d) T₂, (e) T₂’, and (f) apparent diffusion coefficient (ADC) images.

Figure 2. Mean renal blood flow of the (a) right and (b) left kidneys, and (c) heart rate in the supine and upright positions.

Fig 1. Sequential T2* BOLD images acquired in a volunteer during one hour of saline infusion. An anatomical image is shown for reference. The images show clear gradient in tissue oxygenation level between cortex and medulla, represented by higher and lower T2* values, respectively, based on the T2* color map (measured in ms).

Fig 3. Average T2* values (ms) from all volunteers during one hour of saline infusion. Average T2* in the kidney was constant, while T2* values in the cortex were significantly higher than those in the medulla. Note changes in T2* values at the beginning and end of the experiment when infusion rate was lower than the rest of the experiment.

Figure 4. Comparison of representative in vivo R_1ρ dispersion between CL and IRI kidneys. (A) T₂-weighted images (T2W) and R_1ρ maps at different spin-locking strength with locking frequency from 200 to 3000 Hz (top to bottom). (B) Comparison of R_1ρ dispersions between CL and IRI kidneys. The parameters were derived from Chopra model, with fitting results from SL strength ranges 200-3000 Hz shown. Cortex and OSOM were included to calculate the averaged R_1ρ at each spin-lock strength for further fitting.

Figure 5. Representative comparison of MRI images and maps of CL and IRI kidneys. (A) T₂-weighted (T2W) images zoomed on CL and IRI kidneys. (B) R₁, R_1ρ (spin-lock frequency 1000 Hz), R₂, R₂*, pool size ratio (PSR) from quantitative magnetization transfer (qMT) modeling, and magnetization transfer ratio (MTR) based on images without and with magnetization transfer saturation (flip angle 820 degree and RF offset 5000 Hz). The arrows indicate outer medulla.

T1 maps from a healthy volunteer (left) and patient with moderate renal impairment and biopsy-proven fibrosis (right). Lower contrast (ie. smaller T1 different) between cortical and medullary regions is observed in the patient with renal disease compared to the healthy volunteer.

Cortical and medullary T1 (pre- and post-administration of gadolinium-based contrast agent), T2 and T2* measurements from healthy volunteers and patients with moderate renal impairment. ‡ denotes a statistically significant different from healthy controls (p < 0.05).

Fig.1 Regions of interest were drawn manually on the kidney, liver and perirenal fat to obtain the quantitative FF(a). Colour-coded FF maps from a 25-year-old non- Metabolic syndrome male (b) , a 28-year-old male in MS-G1 group (c), and a 40-year-old male in MS-G2 group (d), whose average renal FF are 3.34%, 4.41% and 5.71% respectively .

Fig.2 In groups of control, MS-G1 and MS-G2, renal FF increased gradually and with significant differences among the groups(P<0.01).

Fig1. A 50-year-old male with CKD grade 5,eGFR was 7.87ml/min (1a). T2WI image. (1b)R2* image (1c). FF image.

A 40-year-old male with CKD grade 1,eGFR was 124.09ml/min (1d). T2WI image. (1e)R2* image (1f). FF image

A 31-year-old female volunteer (1g). T2WI image. (1h)R2* image (1i). FF image

Fig2. Diagnostic efficiency curve of the R2* values in heathy controls and mild CKD patients (2a).

Diagnostic efficiency curve of the R2* values in heathy controls and acute CKD patients (2b).

Diagnostic efficiency curve of the FF values in mild CKD patients and acute CKD patients (2c).

Susceptibility maps of both kidneys for DN stage Ⅰ(a), Ⅱ(b) and Ⅲ(c). As the stage of DN increased, the medulla showed stronger diamagnetic value. However, there was no significant changes in the cortex.

Recent studies of MR imaging have shown that water content level of tissue could be evaluated sensitively with T2 mapping 1). Steady-state free precession (SSFP) with spatially selective inversion recovery (ss IR) pulse using multi inversion time (TI) is able to distinct renal corticomedullary differentiation

In two-group comparisons, significant differences were seen between group 0 and group 1 in values of T2 (mean ± SD: 95.8±8.39 vs. 106.4±11.49; p=0.015) T2* (33.4±2.41 vs. 38.3.0±6.31; p=0.020), inverted TI (1205±49.4 vs. 1288±55.3; p=0.001) and optimal TI (1367±61.2 vs. 1450±60.0; p=0.002). Significant differences were seen between group 0 and group 2 in values of T2 (95.8±8.39 vs. 105.7±6.38; p=0.021) T2* (33.4±2.41 vs. 41.4±4.69; p=0.001)

Fig.1 Representative T1 and R2* mapping of the normal (a,b), the mild (c,d) and the moderate to severe patients (e,f) were shown.

Fig. 3 A-C:T1 value was negatively correlated with eGFR, Hb and HCT（p＜0.05）; D-F:T1 value was positively correlated with the NGAL, Scr, SBP（p＜0.05）; G-J: T1 value has no correlation with 24hUpro, BMI, DBP and ALB.

Fig.1 Five typical T2* images of BOLD-MRI in healthy volunteer and CKD1-4 patients. a Healthy volunteer, male/26 years old. b Stage 1 CKD patient, female/28 years old. c Stage 2 CKD patient, male/29 years old. d Stage 3 CKD patient, female/ 62 years old. e Stage 4 CKD patient, female/58 years old.

Fig.2 Correlation coefficients among the cortical T2* (COT2*), outer medullary T2* (OMT2*) values, peak systolic velocity (PSV), and estimated glomerular filtration rate (eGFR). a Correlation of COT2* values and eGFR. b Correlation of OMT2* values and eGFR. c Correlation of PSV values and eGFR. d Correlation of COT2* values and PSV values. e Correlation of OMT2* values and PSV. Spearman coefficient testing was performed to assess statistical significance.

O2-inhalation T2* BOLD MRIR2* map for 67 years man with cardiomyopathy and mild renal dysfunction

Comparison of ΔR2*ratio between patients with eGFR <50mL/min/1.73m2and >50 mL/min/1.73m2(left) and between patient with LVEDVi >95 ml/m2 and <95 ml/m2.

Table2. ROC Curve analysis of Renal allograft function in patients with Group A and Group B, Group B and Control group by IVIM and T1-Mapping

Fig. 1 The Kidney,s selection method of region of interest (ROI). 1a) the upper, middle and lower poles of the kidney are located in the kidney, and several ROIs are delineated in thecortex;1 b) the upper, middle and lower poles of the kidney are located in the kindey, and several ROIs are delineated in the Medulla

Fig.1 Renal T1 maps. A: Coronal native T1 map of two kidneys of a healthy subject, T1=1539ms. B: CKD stage 1, T1=1622ms. C: CKD stage 2, T1=1751ms. D: CKD stage 3, T1=1796ms. E: CKD stage 4, T1=1902ms. F: CKD stage 5, T1=2068ms.

Fig.2 A: T1 value of renal cortex was significantly lower in the HC group than in CKD patients(F=29.62, P＜0.001). Statistical differences of T1 values were found between CKD stages except for stage 2 and 3 (p<0.05). B: Compared to non-fibrosis group, T1 value increased in the low and medium fibrosis group (p<0.05). C: The area under the ROC curve of T1 value for the prediction of IF is 0.762, and the optimal cutoff value of T1 is 1695 ms.

Figure 1. A 55-year-old female volunteer. T2w image (1a), APT image(1b), R2* image(1c). A 34-year-old female with CKD grade 5, eGFR was 3.96, T2w image (2a), APT image(2b), R2* image(2c). A 59-year-old male with CKD grade 1, eGFR was 114.58. T2w image (3a), APT image(3b), R2* image(3c).

Figure 4. Diagnostic efficiency curve of VHs and mRD(4a), diagnostic efficiency curve of VHs and sRD(4b), diagnostic efficiency curve of the APT values in mRD and sRD(4c) , diagnostic efficiency curve of joint use of the APT values and the R2* value in VHs and mRD (4d).

Fig 2. Kidney VAI results. (a) Gradient echo (GE) and spin echo (SE) relaxation time curves from a selected pixel. These signals are fitted before calculation of the hysteresis loops. A clockwise hysteresis loop in this case is generated from the two signal series (b). Six VAI parametric maps are calculated based on the properties of loops and overlaid on gradient echo images (c).

Fig 1. Respiration motion and motion correction in two heathy subjects (top down). M-mode display of navigator data showing abdomen motion with respiration (a, c). Note the signal saturation in the navigator signal caused by imaging slices (a, c). The calculated motion information are overlaid (red curve in a and c). Signal of liver in the last slices are compared before and after motion correction (b, d).

Figure2. Reconstruction of renal artery. The first row, from left to right: SENSE2, CS2-CS4. The second row, from left to right: CS6-CS10.

Figure 1. Location of two ROI of the blood vessels and the renal medulla. Use ROI to measure SI and SD on the left sides. The measured left blood vessel SI value was 1651.55, muscle SI value was 152.66, and muscle SD value was 25.95.

Figure 4. The comparison of mean signal intensities in control (left), label (middle) and difference (right) images of second subject’s kidney (fig. 3) between unbalanced pCASL (blue) and balanced pCASL (red) across different off-resonance.

Figure 2. a) 3D printed phantom mimics the branching vessels with input/output tubes connected to the pump. b) Labeling plane (yellow) and inflow saturation setup (blue) for 2D image acquisition (red). c) and d) Control and label signal pattern among different offset resonances of unbalanced pCASL (ubpCASL) with Gmax to Gave ratio of 10 and 7 respectively.

Figure 2: Frontal views of scan in which upper and lower segmental arteries are injected with water.

Figure 4: Visualization of the renal vascular tree

Fig 1. ROIs are drawn on T2 maps, and manually delineated along the margin of the renal outer medulla (A). The outer medulla is delineated according to the anatomy on the pathological map (B). ROI = region of interest. OM = outer medulla. IM = inner medulla.

Figure: 2

Figure 1. Various b- value images in a normal rat. b = 0, 500, 1000, 1500, and 2000 s/mm2 separately from left to right.

Figure 2. The MK values of the cortex (a), medulla (b), and MD values of the cortex (c), medulla (d) in different groups.

Figure 2

Figure 3

Figure 1. T2WI images acquired at 1 hour (A, E), and at 1 (B, F), 2 (C, G), and 5 (D, H) days after surgery. Figures A-D are sham operation group. Figures E-H are experiment group.

Figure 4. Experimental group graphs at all imaging time points following the cold ischemia-reperfusion injury model. Values of the cortex (CO), outer stripe of outer medulla (OSOM), and inner stripe of outer medulla (ISOM) are averaged over the kidney to give (A) apparent diffusion coefficients [ADC], (B) pure molecular diffusion [D], (C) pseudo-diffusion [D*], and (D) the perfusion fraction. a: versus 1h; b: versus 1d; c: versus 2d; single mark: P<0.05; double mark: P<0.01; *: P<0.05; **: P<0.01

T2-weighted imaging (T2WI) images of the experimental (upper panel) and sham (lower panel) operation groups at 1 hour, 1 day, 2 day, and 5 day (left to right) after the operations to induce renal cold ischemia-reperfusion injury (CIRI).

Column graphs show renal cortical parameter comparisons among the three groups at 1 hour, 1 day, 2 day, 5 day after surgery. ^a and ^b show statistical differences compared with the normal and sham operation groups, respectively (P < 0.05). The apparent diffusion coefficient (ADC), mean diffusivity (MD), real diffusion coefficient (D), and false diffusion coefficient (D_P) values are displayed as ×10^-3mm²/s, and f values as %. The mean kurtosis (MK) parameter has no unit.

Figure 2. CEST data acquisition and contrast measurement. (A) A T₂-weighted image for segmenting the kidneys into the cortex (C), outer medulla (OM), and inner medulla and papilla (IM+P). (B) A Z-spectrum from a cortex fitted with 7-pool Lorentzian functions. The black arrow indicates the urea contrast at +1 ppm. (C) 1 ppm AREX measurements over time at each kidney region. (D) Fold change of 1 ppm AREX induced by saline infusion measured at each kidney region. Error bars indicate standard error mean.

Figure 3. Quantitative MT (qMT) imaging data. (A) Example qMT spectra and fitting from a voxel in the cortex at two saturation powers (green – 220^o flip angle, blue – 820^o). (B) Pool size ratio (PSR) map of a kidney measured before cisplatin injection (week 0) and 4 weeks after multiple cisplatin injections. (C) PSR measurements over time in different anatomical regions in the kidney. Data are presented as mean ± standard error mean.

Figure 2. T1-map of mouse’s kidney in group of Control + Saline (Figure 2a), Control + TPP-TEMPOL (Figure 2b), AKI + Saline (Figure 2c), AKI + TPP-TEMPOL (Figure 2d).

Figure 4. BUN measurement (Figure 4a), Booy weight loss (Figure 4b) of four group. Figure 4c and 4d is the H&E stain for untreated and treated AKI kidney.

Fig. 1: (a-h) A 59-year-old man with a high-grade ccRCC (WHO grade IV) in the left kidney. The lesion (red arrow) showed moderate signal intensity on T2-weighted image (a), (b-h) corresponding parametric maps (ADC, D_s, MD, MK, D_froc, β and μ). (i-p) A 49-year-old woman with a low-grade ccRCC (WHO grade I) in the right kidney. The lesion (red arrow) showed high signal intensity on T2-weighted image (i), (j-p) corresponding parametric maps (ADC, D_s, MD, MK, D_froc, β and μ).

Fig. 3: (a) ROC curves of the diagnostic performance of D_froc, 𝛽, 𝜇, MD and MK values in distinguishing high- from low-grade ccRCCs. (b) ROC curves of the diagnostic performance of ADC and D_s values in distinguishing high- from low-grade ccRCCs.

The axial contrast-enhancement image shows the tumor thrombus after using targeted drugs (figure 4)shrinking compared with before medication(figure 3) and invading the right side wall of IVC.

See above

Table 1 ADC values, FA values of ccRCC and TCC by two observers and ICC values.

Table 2 Comparison of ccRCC and TCC with ADC values and FA values

Fig. 1 The ROI placed in focus area. The white arrow indicated the lesion area. A&B A 55 years old male patient with clear renal cell carcinoma. A was R2* image,the R2* value was 19.5Hz. B was FF image,the FF value was 3.7. B&C A 60 years old female patient of renal angiomyolipoma without visible fat. C was R2* image,the R2* value was 38.7Hz. D was FF image,the FF value was 25.1.

Fig 2.The ROC curve of R2* and FF value to diagnose ccRCC with RAMLwvf.

Table 1: Comparison by metabolic syndrome status in males and females. Variables are summarized by median (IQR). P-values are based on win ratio (LUTS score) or Wilcoxon rank sum test (volume measurements)

Table 2: Comparison by LUTS score in Males and Females. Binary variables are summarized by N (%), quantitative variables by median (IQR). P-values are based on chi-square (met syndrome) or Wilcoxon rank sum test (volume measurements)

Figure 3. The comparison of normalized lactate and normalized pyruvate between knockout and wildtype at different time points.

Figure 2. Temporal changes in metabolites. Normalized lactate for knock-out and normalized pyruvate for wildtype are shown between 4 and 7 week-old

Figure 1. Intravoxel incoherent motion diffusion-weighted MRI parametric maps in a 25-year-old man with AL. (a), ADC mapping. renal cortex ADC= 2.23×10^-3mm²/sec, renal medulla ADC=1.83×10^-3mm²/sec, (b), D mapping. renal cortex D= 2.10×10^-3mm²/sec, renal medulla D=1.70×10^-3mm²/sec, (c), f mapping. renal cortex f= 30.6%, renal medulla f=17.5%, (d), D^* mapping. renal cortex D^*= 62×10^-3mm²/sec, renal medulla D^*=65×10^-3mm²/sec.

Figure 2. Intravoxel incoherent motion diffusion-weighted MRI parametric maps in a 25-year-old volunteer. (a), ADC mapping. renal cortex ADC= 2.34×10^-3mm²/sec, renal medulla ADC=2.13×10^-3mm²/sec, (b), D mapping. renal cortex D= 2.01×10^-3mm²/sec, renal medulla D=1.95×10^-3mm²/sec, (c), f mapping. renal cortex f= 27.2%, renal medulla f=20.0%, (d), D^* mapping. renal cortex D^*= 68×10^-3mm²/sec, renal medulla D^*=63×10^-3mm²/sec.

Table 1 Mean Values of pre- and post-NAC, and percentage increases in ADC, Between Responders and Non-responders

Figure 1: Images obtained in a 69-year-old man with muscular invasive bladder cancer who was a responder (pT2N0M0). (a, d) pre-NAC (a) and post-NAC (d) Axial T2 weighted image. (b, e) pre-NAC (b) and post-NAC (e) DWI Imaging (b=1000 s/mm²). In b, maximal diameter of the hyperintense signal mass was 2.6 cm. In e, tumor regressed with a maximum diameter of 0.6cm. The tumor diameter was reduced by 77%. (c, f) pre-NAC (c) and post-NAC (f) ADC maps. In c, the mass mean ADC was 1.21×10 ^-3 mm²/s. In f, NAC increased the mean ADC of this lesion to 2.11×10 ^-3 mm²/s.