Kinetic studies of complex biomedical process by magnetic resonance: Cuban experiences

Kinetic studies of complex biomedical process by magnetic resonance: Cuban experiences Applied Appl Magn Reson (2018) 49:589–598 Magnetic Resonance https://doi.org/10.1007/s00723-018-0985-2 ORIGINAL PAPER Kinetic studies of complex biomedical process by magnetic resonance: Cuban experiences 1,2 1 1 Carlos Cabal Mirabal  · Adolfo Fernández García  · Manuel Lores Guevara  · 2 2 Evelio González  · Leonardo Oramas Díaz Received: 24 October 2017 / Revised: 29 January 2018 / Published online: 26 March 2018 © The Author(s) 2018 Abstract The potentials of the magnetic resonance (MR) methods in the research of biomedical systems have been demonstrated during the 70 years of its existence. It is presented that the Cuban experience in quantitative magnetic resonance asso- ciated with molecular, preclinical and clinical studies of significant diseases and drugs development. MR “in vitro” and “in vivo” studies of sickle cell disease, the diabetic foot ulcer, the brain tumor response and the magnetic nano-particle phar- macokinetics, are presented as example. Furthermore, contributions and restrictions of magnetic resonance to diagnostic and optimization of therapeutic pathways are discussed in some concrete cases. 1 Introduction The potentials of the magnetic resonance (MR) methods in the research of biomedi- cal system have been demonstrated during the 70 years of its existence, which it is celebrating during these years. It is presented that the Cuban experience in quantita- tive magnetic resonance associated with molecular, preclinical and clinical studies of significant diseases and drugs development. MR “in vitro” and “in vivo” studies of sickle cell disease (SCD) [1–4], the dia- betic foot ulcer (DFU) [5, 6], the brain tumor (BT) response [8] and the magnetic nano-particle pharmacokinetics (PK-MNP) [10] are presented as illustration. Fur- thermore, contributions and limitations of MR to diagnostic and selection of thera- peutic pathways are discussed. * Carlos Cabal Mirabal carlos.cabal@infomed.sld.cu Medical Biophysics Center, University of Oriente, Santiago de Cuba, Cuba Center for Genetic Engineering and Biotechnology, Havana, Cuba 1 3 590 C. Cabal Mirabal et al. Common purposes of these investigations were to set up the necessary method- ologies for the MR quantitative studies of complex pathological scenario. 2 Materials and methods 2.1 Study subjects The present studies were entirely reviewed and approved by the ethics committee of the different medical institutions and of the research centers that are involved in, according to the ethical principles of the Word Medical Association (Declaration of Helsinki). The written informed consent of the healthy volunteers and the patient was obtained before inclusion in all cases. The studies were carried out following the ethical norms for the use of the laboratory animals; the Guides of Laboratory Good Practices and the Standard Operation Procedures. The detailed description of the “Materials and methods” of MR “in vitro” studies of SCD is presented in Ref. [1–4]. Likewise, for the DFU, BT responses and PK- MNP have been published in Ref. [5, 6, 8, 10], respectively. The main common idea of all these works is to optimize the experiments keep- ing, as constant as possible, all the conditions including the position of the bio- logical sample. In each case, well-characterized external and internal markers, as references, have been establishing to have a control of the subject’s position and bio- logical changes during the kinetic studies. 2.2 SCD studies In vitro magnetic relaxation studies were performed with a Cuban relaxometer. H T1 and T2 at 4 MHz were determinate using inversion recovery (IR), spin echo (SE) and Carr–Purcell–Meiboon–Gil (CPMG) pulse sequences with an error less than 5%. A Varian E-109 Century (X band) spectrometer was employed to determine the saturation transfer spectra of the hemoglobin (Hb) bound radical in HbA and HbS samples as is described in Ref. [3]. H relaxation and ESR measurements were per- formed during 8 h of the spontaneous deoxygenation of blood sample of more than 80 patients at 36 °C [1–4]. 2.3 DFU and BTR studies MRI and MRS “in vivo” studies were performed with a 1.5 T Symphony Master Class system (Siemens). Before each study, the pulse sequences were optimized by means of phantom having T1 and T2 close to biological subject characteristics, as well as, with the contribution of healthy volunteers [5, 7, 8, 10]. A MR study of ten DFU patients were done before and during the intralesional epidermal growth factor (EGF) treatment until the lesion was totally closed [7]. A special device was created to be placed inside the head radiofrequency (RF) coil to guarantee and control the reproducibility of the feet positioning. It was 1 3 Kinetic studies of complex biomedical process by magnetic… demonstrated that the RF coil parameters (Q and B1 homogeneity) did not change [5, 6]. In the device, both feet are fix at the same time allowing simultaneously MRI images without changes in the experimental conditions. Each foot serves as a refer- ence for the other. The device provides two affixed sets of external markers. These markers are connected with internal anatomic markers as a foot position Ref. [5, 6]. As well the device allows controlling the different anatomical foot structure position related to the cited external maker. In Ref. [5, 6] is discussed in more details the relationship between the internal and external marker for control of the foot position during the kinetic MRI studies. Fourteen pediatric patients treated with monoclonal antibody nimotuzumab [9] were evaluated by MRI and MRS for more than 2 years. Each patient was their own control [8]. 2.4 PK‑MNP chemically modified with polyethylene glycol (PEG) Measuring the signal noise ratio (SNR), contrast noise ratio (CNR) and non-images uniformity (NUI) in 1.5  T MRI clinical machine was selected the best RF coil. It was achieved using a phantom having the same dimension and similar T1 and T2 characteristics of rats. Between the head and flexible coils, the flexible one was bet- ter by more than 25%. MNP solutions relaxivities (r and r ) was determinate “in vitro” and “in vivo” by 1 2 MR relaxation and MRI [10]. Before the MRI examination, all Wistar rats (n = 4) have been weighted to deter- minate the MNP and the anesthetic doses as described in Ref. [10]. The MNP-PEG- (NH2)2 doses used was 5 mg/kg (n = 2) and 2.5 mg/kg (n = 2) of animal weight. Before, all the MNP samples were homogenized by ultrasound for 2 min. The injec- tion of the NP-PEG-(NH2)2 was through tail vein. Immediately after the anesthesia, the two rats were collocated and immobilized in a rubber special device enclosed in the RF coil. The rat’s couple in one RF coil permit to increase the SNR. At the same time, one rat was reference for the other, in exactly the same conditions during the experiment. Each couple of rats have been MRI scanned simultaneously just before the injec- tion of NP-PEG-(NH2)2. These images have been considerate as the t = 0 images. After the first and single injection, the rat’s liver MRI imaging were scanned peri- odically until 528 h (22 days). 3 Results and discussion 3.1 MR relaxation and electron spin resonance studies of SCD SCD is the first molecular disease described. Due to the polymerization of HbS, the erythrocyte is deformed, the permeability and elasticity of the membrane change, 1 3 592 C. Cabal Mirabal et al. Fig. 1 a Typical T1and T2 temporal behaviors in HbA and HbS samples (at intracellular concentration and 36  °C). The continuous lines represent the linear and sigmoidal fittings corresponding to the HbA and HbS samples, respectively. In HbS, stage I corresponds with the nucleation, where most molecular aggregation are reversible; stage II corresponds with the irreversible development of polymerization, and the stage III, with the formation of micro-domains [2]. b Typical behavior of  in samples studied by ESR [3].The solid lines represent the sigmoidal and linear fitting that characterize the result obtained in HbS and HbA, respectively. Filled square: T2 HbS, open square: T1 HbS, open circle: T1 HbA, filled circle: T2 HbA [2, 3] Table 1 Rotation correlation time and micro-viscosity determined by ESR [3] Parameter Región I (HbS) Región II (HbS) Región III (HbS) HBA −8 (× 10 ) 5 ± 0.11 5 ± 0.11 ≤   ≤ 9.8 ± 0.22 9.8 ± 0.22 5.8 ± 0.13 R R ƞ (mPas) 2.06 ± 0.1 2.06 ± 0.1 ≤ ƞ ≤ 3.79 ± 0.19 3.79 ± 0.19 2.06 ± 0.1 hemolysis is caused and rheology is modified, leading to painful vaso-occlusive cri- ses [1, 4]. Typical T1 and T2 temporal behaviors in HbA and HbS samples are shown in Fig.  1a [2, 3]. The kinetic of deoxyHbS polymerization is characterized by three stages: initial (I), nucleation (II) and termination (III) (1–4). The initial phase is delimited by the delay time (t ) [1–4]. After, the t takes place an autocatalytic HbS d d polymerization. Once nucleation concludes, H relaxation tends to stabilize (III). The different MR behavior in HbA and HbS solutions could be associated with: (1) the molecular mobility changes. (2) Hb’s magnetism variations (oxyHb: diamag- netic and deoxyHbS: paramagnetic) and (3) the appearance of micro in homogenei- ties at the end of the polymerization process [2, 3]. However, the relative constant of the T1 and T2 for HbA samples excludes the possibility of HbS magnetism varia- tions influence of the magnetic properties of the Hb complexes. The different possible relaxation mechanism was discussed in Ref. [2] concluding that probably the dipole–dipole interactions is the most important. If it is assumed that the dipole–dipole interaction is the main mechanism then from the T1, T2 and T1/T2 ratio values, in the regions I–III, can make an assessment and conclude that −8 ≈ 4 × 10 s. A more precise quantitative evaluation of  variation was done by ESR. Table  1 and Fig.  1b present the values and temporal behavior of  and 1 3 Kinetic studies of complex biomedical process by magnetic… determinate by ESR [3]. It is a good agreement between the H MR relaxation and ESR by the spin labeling method data. The strong existing correlation between the MR parameters (T1, T2, ,  ) with the t has allowed us to stablish a new diagnostic method for the differentia- tion between the crises and steady stages of the patients [4]. A decrease of t (32%) can be observed during painful crisis conditions in the same sickle cell patients (see Fig. 2a). As summarized in Fig. 2b, a similar result was obtained for all patients studied under painful crisis conditions, in which the mean value of the relative differentiation of t with respect to steady state condi- tion is 36 ± 10%. It means that it can be established a differentiation between both clinical conditions when you compare the t value of one patient during crisis with his own t value during steady state. As it is concluded in Ref. [4] H relaxa- tion method can be used to differentiate steady state and crisis clinical conditions. Furthermore, this MR procedure made possible the discovery of the anti- sickling action of 4-hydroxy-3-methoxybenzaldehyde (Vanillin, a nontoxic com- pound) as a therapeutic drug, as it was established in Ref. [1, 4]. The anti-sick- ling action on polymerization of vanillin was demonstrated “in vivo” in a double blind, placebo-controlled clinical therapeutic trial performed in 30 patients (11 belonging to the control group), through the increment of the t on average 1.6 times indicating a decrease in the effectiveness of the polymerization process [1 , 4]. Fig. 2 a Typical temporal behavior and t values related the steady stage and in painful crisis clinical conditions, for the same pediatric patient. The black box curves correspond to the crisis. The relative differentiation between both t values is 32% for this case [4]. b Delay time values corresponding to the steady and painful crisis clinical conditions stages for ten pediatric sickle cell patients. The gray hori- zontal lines represent the t limits corresponding to the steady and crisis regions. The uncertainty region includes the 15% of the measured values [4] 1 3 594 C. Cabal Mirabal et al. 3.2 MRI/MRS quantitative evaluation of DFU response under treatment in clinical studies The changes of DFU lesion sizes (area and volume), edema (volume), as well as apparent diffusion coefficient (ADC), and metabolites spectra, as a function of the EGF treatment time, were reported during a clinical trial phase IV [5]. As example in the Fig.  3, the ADC data as a function of the treatment time is presented for one of the patient. The described device fixes both feet at the same time allowing MRI images simultaneously. Then, each foot can be a reference for the other [5, 6]. In Fig. 3 are shown the three ADC time-dependent curves corre- sponding to: healthy foot (in red), DFU (in blue), and the free water ADC (in the top, in black), as control. These plots demonstrate that DFU ADC curves show a trend toward the healthy foot values during the treatment time. If the measurements are performed under identical conditions (foot position, pulse sequence, slice orientation, etc.), we could hypothesize that ADC-relative changes are connected to the tissue texture differences and others physio-path- ological features; regardless of ADC complex dependence on tissue character- istics. This was the first report of ADC and edema evolution of the DFU under treatment. The ADC data are in agreement with the edema that reported each micro-region or voxel in the foot. Whichever, this procedure is useful for evolu- tion studies of other pedal and tissue disorders [5]. All MRI/MRS data obtained are in accordance with clinical observation. Moreover, the obtained quantitative information permits to understand several healing mechanism at tissue level and to optimize the treatment procedure. Fig. 3 Calculated ADC from DWI, as a function of the treatment time (in weeks), for one patient. The ADC of the healthy foot is shown in red. The blue line represents the ADC of the DFU and the black line denotes the free water ADC [5] 1 3 Kinetic studies of complex biomedical process by magnetic… 3.3 MRI/MRS quantitative evaluation of BT response under treatment in clinical studies The characterization of the evolution of the tumor lesion was made from the fol- lowing magnitudes and parameters obtained from MRI: 1. Volume of the lesion visualized in the T1 (V ), T2 (V ) and FLAIR (V ) T1 T2 FLAIR images. A more accurate evolutionary study is possible using these different volumes, as they are associated with different tumor cell densities and textures. Using these different volumes, a more accurate evolutionary study is possible as a consequence that they associated with different tumor cell densities and textures. The following volume ratios were calculated: V /V , V /V , V /V . T2 T1 FLAIR T1 T2 FLAIR An example of lesion volume evaluation (V , V and V ) in patient 12 is T1 T2 FLAIR given in Fig. 4. These different volumes correspond to diverse molecular mobility and cell densities in the tumor region. Evidently, there are complex correlations between the relaxation times, the different mean spectral density function values and the physio-pathological characteristics of the tumor response. Nevertheless, the com- parison between lesion volumes obtained from different image contrast contains more information about the lesion state, beyond the simple volume acquired from one image type with and without CA. The real quantitative separation of the different molecular and cellular mobili- ties associated with the different pathological tissue regions is one of the unsolved problems regarding these complex pathologies. Many efforts are been made to overcome this essential problem for MRI diagnostic. It is possible to attenuate, or in some cases, to avoid this limitations having robust protocol, decreasing the image time, using external and internal markers and by means of multi-paramet- ric images. Nowadays, a real T1, T2 “in vivo” map is a great challenge to the quantitative MRI. Before Nimotuzumab treatmentAfter treatment 3 years and 3 months 3 years and 6 months V 1356663595027 T1 V mm 9618133510 34566 T2 V 139698 1866220514 FLAIR Fig. 4 Illustration of a calculated tri-dimensional representation of images of patient no. 12 with a brain stem tumor. The lesion is labelled in T1 (red), T2 (magenta) and FLAIR (purple) [8] Gd 1 3 596 C. Cabal Mirabal et al. 2. In the previous mentioned sense, the ADC maps are important information to the understanding of the relaxation and molecular mechanism connected to each different tumor regions. Quantitative ADC maps, related to the water mobility, for the lesion and for its surroundings were obtained for the patients under study, before and during the treatment [8]. 3. Amplitude ratios of N-acetyl aspartate (NAA), choline (Cho) and creatine metabo- lite peaks. Lesion and healthy areas located in the contra-lateral hemisphere were studied. The NAA/Cr, Cho/NAA and Cho/NAA ratios were retrospectively evalu- ated for each patient, and used as one of the evaluating criteria [8]. The present MRI/MRS results are in good agreement with the clinical evaluation and confirm once again the MR possibilities when a standardized robust protocol is used [8]. The MRI/MRS data gave distinctive complementary information related to the BT response during long treatment time to delimit the treatment conduct and contribute in the understanding of bio-physiological process associated with the anti-tumor mechanism of the drugs. 3.4 MNP. Pharmacokinetics (PK) by MR relaxation and MRI Nowadays, MNPs are applied for diagnosis, drug delivery and thermotherapy agents amongst others. MRI is a complementary technique to follow PK of MNP [10]. In Fig. 5 is represented the dependence of the ratio (I  − I )/I , proportional to i 0 0 MNP concentration. The measured image intensities I were normalized to the background I and the ratio (I   −  I )/I was calculated as a time function after 0 i 0 0 MNP injection. Two different areas of the liver were evaluated (red and blue Fig. 5 Dependence of the I /(I  − I ) ratio (proportional to the MNP concentration) as a function of time 0 i 0 after MNP injection. Two different areas of the liver were measured (red and blue lines) and, as a control, a muscle area was taken (line pink line) [10] 1 3 Kinetic studies of complex biomedical process by magnetic… lines) and one muscle area (pink line) was taken as control. The graphics have three regions with different slopes. The first one, which is associated with the entrance of the MNP in the liver: absorption period. The second one can be attrib- uted to the liver stationary state: residence. Finally, the last region is connected to the MNP excretion. From these measurements, it was possible to determine the principal MNP PK parameters as reported in Ref. [10]. A new metabolic route of MNP “in vivo” bio-distribution was described in base of this data. Nonetheless, the MNP MR “in vivo” studies are limited as con- sequence of the strength “negative contrast” introduced by MNP in T2 relaxation mechanism. It is necessary to make some complementary effort to overcome this restriction. 4 Conclusion “In vitro” and “in vivo” MR data gave unique complementary information related to the kinetic studies of complex biomedical processes. MR has contributed to the discovery of new pathways and drugs for treatment and to introduce modification in them. Furthermore, MR provides valuable information on bio-processes that occur over long periods of time, contributing to the understanding of the physi- ological processes and delimiting the treatment conduct. Nonetheless, the real quantitative separation of the different mobility’s (molec- ular and cellular), the metabolic activity, associated with the different pathologi- cal tissues regions still be an unsolved problem related to complex pathologies. This essential and complex MRI problem need many effort to be overcome. Nowadays, to obtain a real quantitative T1, T2, Diffusion and metabolic maps “in vivo”, in real time, is still a great challenge to the MR. Nevertheless, it is possible to attenuate, or some cases to avoid these restric- tions by having robust and standard protocols, decreasing the image time, by means of external and internal markers, employing adequate and well-character- ized phantoms and via the multi-parametric images among other procedures. In addition, adequate preparation for the technicians and medical experts working in MR is a success factor for achieving these proposes. Acknowledgements We are grateful to Lora Hospital, Santiago de Cuba and to the Medical-Surgi- cal-Research Center, Havana. Likewise, thanks to patients, volunteers and coworkers related to these studies. Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 Inter- national License (http://creat iveco mmons .org/licen ses/by/4.0/), which permits unrestricted use, distribu- tion, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made. References 1. A. Fernández, C. Cabal, J. Losada, E. Alvarez, C. Soler, J. Otero, Hemoglobin A 29, 181 (2005) 1 3 598 C. Cabal Mirabal et al. 2. M. Lores, C. Cabal, Appl. Magn. Reson. A 28, 1 (2005) 3. M. Lores, C. Cabal, O.R. Nascimento, A.M. Gennaro, Appl. Magn. Reson. 30, 121–128 (2006) 4. A. Fernandez, C. Cabal, M. Lores, J. Losada, E. Perez, Hemoglobin A 33, 206 (2009) 5. C. Cabal-Mirabal, E. González Dalmau, J. Berlanga Acosta, D. Darias Zayas, L. Herrera Mar- tínez, P. Lopez Saura, G. Guillén Nieto, J. Baldomero Hernández, C. González Delgado, L. Javier González, J. Radiol. Res. Pract. (2014). https ://doi.org/10.5171/2014.78398 0 6. C. Cabal-Mirabal, E. Gonzalez, L. Manuel Flores, J. Berlanga Acosta, L. Herrera Martinez, United State Patent Application Publication. US2016/0157750 (2016) 7. J. Berlanga Acosta, W. Savigne, C. Valdez, N. Franco, J. S. Alba, A. del Rio, P. Lopez-Saura, G. Guillen, E. Lopez, L. Herrera Martinez, J. Fernandez-Montequın, Int. Wound J. A 3, 232 (2006) 8. E. González Dalmau, C. Cabal-Mirabal, G. Sáurez Martínez, A. Lage Dávila, J. Ugarte Suarez, R. Cabanas Armada, G. Rodríguez Cruz, D. Darias Zayas, M. Rios Castillo, L. Valle Garrido, Pediatr. Int. (2014). https ://doi.org/10.1111/ped.12212 9. U. Bode, M. Massimino, F. Bach, M. Zimmermann, E. Khuhlaeva, M. Westphai, K. Fleischhack, Expert Opin. Biol. Ther. 12, 1649 (2012) 10. A. Ruiz, Y. Hernández, C. Cabal, E. González, S. Veintemillas-Verdaguer, E. Martinez, M.P. Morales, Nanoscale (2013). https ://doi.org/10.1039/c3nr0 1412f 1 3 http://www.deepdyve.com/assets/images/DeepDyve-Logo-lg.png Applied Magnetic Resonance Springer Journals

Kinetic studies of complex biomedical process by magnetic resonance: Cuban experiences

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Applied Appl Magn Reson (2018) 49:589–598 Magnetic Resonance https://doi.org/10.1007/s00723-018-0985-2 ORIGINAL PAPER Kinetic studies of complex biomedical process by magnetic resonance: Cuban experiences 1,2 1 1 Carlos Cabal Mirabal  · Adolfo Fernández García  · Manuel Lores Guevara  · 2 2 Evelio González  · Leonardo Oramas Díaz Received: 24 October 2017 / Revised: 29 January 2018 / Published online: 26 March 2018 © The Author(s) 2018 Abstract The potentials of the magnetic resonance (MR) methods in the research of biomedical systems have been demonstrated during the 70 years of its existence. It is presented that the Cuban experience in quantitative magnetic resonance asso- ciated with molecular, preclinical and clinical studies of significant diseases and drugs development. MR “in vitro” and “in vivo” studies of sickle cell disease, the diabetic foot ulcer, the brain tumor response and the magnetic nano-particle phar- macokinetics, are presented as example. Furthermore, contributions and restrictions of magnetic resonance to diagnostic and optimization of therapeutic pathways are discussed in some concrete cases. 1 Introduction The potentials of the magnetic resonance (MR) methods in the research of biomedi- cal system have been demonstrated during the 70 years of its existence, which it is celebrating during these years. It is presented that the Cuban experience in quantita- tive magnetic resonance associated with molecular, preclinical and clinical studies of significant diseases and drugs development. MR “in vitro” and “in vivo” studies of sickle cell disease (SCD) [1–4], the dia- betic foot ulcer (DFU) [5, 6], the brain tumor (BT) response [8] and the magnetic nano-particle pharmacokinetics (PK-MNP) [10] are presented as illustration. Fur- thermore, contributions and limitations of MR to diagnostic and selection of thera- peutic pathways are discussed. * Carlos Cabal Mirabal carlos.cabal@infomed.sld.cu Medical Biophysics Center, University of Oriente, Santiago de Cuba, Cuba Center for Genetic Engineering and Biotechnology, Havana, Cuba 1 3 590 C. Cabal Mirabal et al. Common purposes of these investigations were to set up the necessary method- ologies for the MR quantitative studies of complex pathological scenario. 2 Materials and methods 2.1 Study subjects The present studies were entirely reviewed and approved by the ethics committee of the different medical institutions and of the research centers that are involved in, according to the ethical principles of the Word Medical Association (Declaration of Helsinki). The written informed consent of the healthy volunteers and the patient was obtained before inclusion in all cases. The studies were carried out following the ethical norms for the use of the laboratory animals; the Guides of Laboratory Good Practices and the Standard Operation Procedures. The detailed description of the “Materials and methods” of MR “in vitro” studies of SCD is presented in Ref. [1–4]. Likewise, for the DFU, BT responses and PK- MNP have been published in Ref. [5, 6, 8, 10], respectively. The main common idea of all these works is to optimize the experiments keep- ing, as constant as possible, all the conditions including the position of the bio- logical sample. In each case, well-characterized external and internal markers, as references, have been establishing to have a control of the subject’s position and bio- logical changes during the kinetic studies. 2.2 SCD studies In vitro magnetic relaxation studies were performed with a Cuban relaxometer. H T1 and T2 at 4 MHz were determinate using inversion recovery (IR), spin echo (SE) and Carr–Purcell–Meiboon–Gil (CPMG) pulse sequences with an error less than 5%. A Varian E-109 Century (X band) spectrometer was employed to determine the saturation transfer spectra of the hemoglobin (Hb) bound radical in HbA and HbS samples as is described in Ref. [3]. H relaxation and ESR measurements were per- formed during 8 h of the spontaneous deoxygenation of blood sample of more than 80 patients at 36 °C [1–4]. 2.3 DFU and BTR studies MRI and MRS “in vivo” studies were performed with a 1.5 T Symphony Master Class system (Siemens). Before each study, the pulse sequences were optimized by means of phantom having T1 and T2 close to biological subject characteristics, as well as, with the contribution of healthy volunteers [5, 7, 8, 10]. A MR study of ten DFU patients were done before and during the intralesional epidermal growth factor (EGF) treatment until the lesion was totally closed [7]. A special device was created to be placed inside the head radiofrequency (RF) coil to guarantee and control the reproducibility of the feet positioning. It was 1 3 Kinetic studies of complex biomedical process by magnetic… demonstrated that the RF coil parameters (Q and B1 homogeneity) did not change [5, 6]. In the device, both feet are fix at the same time allowing simultaneously MRI images without changes in the experimental conditions. Each foot serves as a refer- ence for the other. The device provides two affixed sets of external markers. These markers are connected with internal anatomic markers as a foot position Ref. [5, 6]. As well the device allows controlling the different anatomical foot structure position related to the cited external maker. In Ref. [5, 6] is discussed in more details the relationship between the internal and external marker for control of the foot position during the kinetic MRI studies. Fourteen pediatric patients treated with monoclonal antibody nimotuzumab [9] were evaluated by MRI and MRS for more than 2 years. Each patient was their own control [8]. 2.4 PK‑MNP chemically modified with polyethylene glycol (PEG) Measuring the signal noise ratio (SNR), contrast noise ratio (CNR) and non-images uniformity (NUI) in 1.5  T MRI clinical machine was selected the best RF coil. It was achieved using a phantom having the same dimension and similar T1 and T2 characteristics of rats. Between the head and flexible coils, the flexible one was bet- ter by more than 25%. MNP solutions relaxivities (r and r ) was determinate “in vitro” and “in vivo” by 1 2 MR relaxation and MRI [10]. Before the MRI examination, all Wistar rats (n = 4) have been weighted to deter- minate the MNP and the anesthetic doses as described in Ref. [10]. The MNP-PEG- (NH2)2 doses used was 5 mg/kg (n = 2) and 2.5 mg/kg (n = 2) of animal weight. Before, all the MNP samples were homogenized by ultrasound for 2 min. The injec- tion of the NP-PEG-(NH2)2 was through tail vein. Immediately after the anesthesia, the two rats were collocated and immobilized in a rubber special device enclosed in the RF coil. The rat’s couple in one RF coil permit to increase the SNR. At the same time, one rat was reference for the other, in exactly the same conditions during the experiment. Each couple of rats have been MRI scanned simultaneously just before the injec- tion of NP-PEG-(NH2)2. These images have been considerate as the t = 0 images. After the first and single injection, the rat’s liver MRI imaging were scanned peri- odically until 528 h (22 days). 3 Results and discussion 3.1 MR relaxation and electron spin resonance studies of SCD SCD is the first molecular disease described. Due to the polymerization of HbS, the erythrocyte is deformed, the permeability and elasticity of the membrane change, 1 3 592 C. Cabal Mirabal et al. Fig. 1 a Typical T1and T2 temporal behaviors in HbA and HbS samples (at intracellular concentration and 36  °C). The continuous lines represent the linear and sigmoidal fittings corresponding to the HbA and HbS samples, respectively. In HbS, stage I corresponds with the nucleation, where most molecular aggregation are reversible; stage II corresponds with the irreversible development of polymerization, and the stage III, with the formation of micro-domains [2]. b Typical behavior of  in samples studied by ESR [3].The solid lines represent the sigmoidal and linear fitting that characterize the result obtained in HbS and HbA, respectively. Filled square: T2 HbS, open square: T1 HbS, open circle: T1 HbA, filled circle: T2 HbA [2, 3] Table 1 Rotation correlation time and micro-viscosity determined by ESR [3] Parameter Región I (HbS) Región II (HbS) Región III (HbS) HBA −8 (× 10 ) 5 ± 0.11 5 ± 0.11 ≤   ≤ 9.8 ± 0.22 9.8 ± 0.22 5.8 ± 0.13 R R ƞ (mPas) 2.06 ± 0.1 2.06 ± 0.1 ≤ ƞ ≤ 3.79 ± 0.19 3.79 ± 0.19 2.06 ± 0.1 hemolysis is caused and rheology is modified, leading to painful vaso-occlusive cri- ses [1, 4]. Typical T1 and T2 temporal behaviors in HbA and HbS samples are shown in Fig.  1a [2, 3]. The kinetic of deoxyHbS polymerization is characterized by three stages: initial (I), nucleation (II) and termination (III) (1–4). The initial phase is delimited by the delay time (t ) [1–4]. After, the t takes place an autocatalytic HbS d d polymerization. Once nucleation concludes, H relaxation tends to stabilize (III). The different MR behavior in HbA and HbS solutions could be associated with: (1) the molecular mobility changes. (2) Hb’s magnetism variations (oxyHb: diamag- netic and deoxyHbS: paramagnetic) and (3) the appearance of micro in homogenei- ties at the end of the polymerization process [2, 3]. However, the relative constant of the T1 and T2 for HbA samples excludes the possibility of HbS magnetism varia- tions influence of the magnetic properties of the Hb complexes. The different possible relaxation mechanism was discussed in Ref. [2] concluding that probably the dipole–dipole interactions is the most important. If it is assumed that the dipole–dipole interaction is the main mechanism then from the T1, T2 and T1/T2 ratio values, in the regions I–III, can make an assessment and conclude that −8 ≈ 4 × 10 s. A more precise quantitative evaluation of  variation was done by ESR. Table  1 and Fig.  1b present the values and temporal behavior of  and 1 3 Kinetic studies of complex biomedical process by magnetic… determinate by ESR [3]. It is a good agreement between the H MR relaxation and ESR by the spin labeling method data. The strong existing correlation between the MR parameters (T1, T2, ,  ) with the t has allowed us to stablish a new diagnostic method for the differentia- tion between the crises and steady stages of the patients [4]. A decrease of t (32%) can be observed during painful crisis conditions in the same sickle cell patients (see Fig. 2a). As summarized in Fig. 2b, a similar result was obtained for all patients studied under painful crisis conditions, in which the mean value of the relative differentiation of t with respect to steady state condi- tion is 36 ± 10%. It means that it can be established a differentiation between both clinical conditions when you compare the t value of one patient during crisis with his own t value during steady state. As it is concluded in Ref. [4] H relaxa- tion method can be used to differentiate steady state and crisis clinical conditions. Furthermore, this MR procedure made possible the discovery of the anti- sickling action of 4-hydroxy-3-methoxybenzaldehyde (Vanillin, a nontoxic com- pound) as a therapeutic drug, as it was established in Ref. [1, 4]. The anti-sick- ling action on polymerization of vanillin was demonstrated “in vivo” in a double blind, placebo-controlled clinical therapeutic trial performed in 30 patients (11 belonging to the control group), through the increment of the t on average 1.6 times indicating a decrease in the effectiveness of the polymerization process [1 , 4]. Fig. 2 a Typical temporal behavior and t values related the steady stage and in painful crisis clinical conditions, for the same pediatric patient. The black box curves correspond to the crisis. The relative differentiation between both t values is 32% for this case [4]. b Delay time values corresponding to the steady and painful crisis clinical conditions stages for ten pediatric sickle cell patients. The gray hori- zontal lines represent the t limits corresponding to the steady and crisis regions. The uncertainty region includes the 15% of the measured values [4] 1 3 594 C. Cabal Mirabal et al. 3.2 MRI/MRS quantitative evaluation of DFU response under treatment in clinical studies The changes of DFU lesion sizes (area and volume), edema (volume), as well as apparent diffusion coefficient (ADC), and metabolites spectra, as a function of the EGF treatment time, were reported during a clinical trial phase IV [5]. As example in the Fig.  3, the ADC data as a function of the treatment time is presented for one of the patient. The described device fixes both feet at the same time allowing MRI images simultaneously. Then, each foot can be a reference for the other [5, 6]. In Fig. 3 are shown the three ADC time-dependent curves corre- sponding to: healthy foot (in red), DFU (in blue), and the free water ADC (in the top, in black), as control. These plots demonstrate that DFU ADC curves show a trend toward the healthy foot values during the treatment time. If the measurements are performed under identical conditions (foot position, pulse sequence, slice orientation, etc.), we could hypothesize that ADC-relative changes are connected to the tissue texture differences and others physio-path- ological features; regardless of ADC complex dependence on tissue character- istics. This was the first report of ADC and edema evolution of the DFU under treatment. The ADC data are in agreement with the edema that reported each micro-region or voxel in the foot. Whichever, this procedure is useful for evolu- tion studies of other pedal and tissue disorders [5]. All MRI/MRS data obtained are in accordance with clinical observation. Moreover, the obtained quantitative information permits to understand several healing mechanism at tissue level and to optimize the treatment procedure. Fig. 3 Calculated ADC from DWI, as a function of the treatment time (in weeks), for one patient. The ADC of the healthy foot is shown in red. The blue line represents the ADC of the DFU and the black line denotes the free water ADC [5] 1 3 Kinetic studies of complex biomedical process by magnetic… 3.3 MRI/MRS quantitative evaluation of BT response under treatment in clinical studies The characterization of the evolution of the tumor lesion was made from the fol- lowing magnitudes and parameters obtained from MRI: 1. Volume of the lesion visualized in the T1 (V ), T2 (V ) and FLAIR (V ) T1 T2 FLAIR images. A more accurate evolutionary study is possible using these different volumes, as they are associated with different tumor cell densities and textures. Using these different volumes, a more accurate evolutionary study is possible as a consequence that they associated with different tumor cell densities and textures. The following volume ratios were calculated: V /V , V /V , V /V . T2 T1 FLAIR T1 T2 FLAIR An example of lesion volume evaluation (V , V and V ) in patient 12 is T1 T2 FLAIR given in Fig. 4. These different volumes correspond to diverse molecular mobility and cell densities in the tumor region. Evidently, there are complex correlations between the relaxation times, the different mean spectral density function values and the physio-pathological characteristics of the tumor response. Nevertheless, the com- parison between lesion volumes obtained from different image contrast contains more information about the lesion state, beyond the simple volume acquired from one image type with and without CA. The real quantitative separation of the different molecular and cellular mobili- ties associated with the different pathological tissue regions is one of the unsolved problems regarding these complex pathologies. Many efforts are been made to overcome this essential problem for MRI diagnostic. It is possible to attenuate, or in some cases, to avoid this limitations having robust protocol, decreasing the image time, using external and internal markers and by means of multi-paramet- ric images. Nowadays, a real T1, T2 “in vivo” map is a great challenge to the quantitative MRI. Before Nimotuzumab treatmentAfter treatment 3 years and 3 months 3 years and 6 months V 1356663595027 T1 V mm 9618133510 34566 T2 V 139698 1866220514 FLAIR Fig. 4 Illustration of a calculated tri-dimensional representation of images of patient no. 12 with a brain stem tumor. The lesion is labelled in T1 (red), T2 (magenta) and FLAIR (purple) [8] Gd 1 3 596 C. Cabal Mirabal et al. 2. In the previous mentioned sense, the ADC maps are important information to the understanding of the relaxation and molecular mechanism connected to each different tumor regions. Quantitative ADC maps, related to the water mobility, for the lesion and for its surroundings were obtained for the patients under study, before and during the treatment [8]. 3. Amplitude ratios of N-acetyl aspartate (NAA), choline (Cho) and creatine metabo- lite peaks. Lesion and healthy areas located in the contra-lateral hemisphere were studied. The NAA/Cr, Cho/NAA and Cho/NAA ratios were retrospectively evalu- ated for each patient, and used as one of the evaluating criteria [8]. The present MRI/MRS results are in good agreement with the clinical evaluation and confirm once again the MR possibilities when a standardized robust protocol is used [8]. The MRI/MRS data gave distinctive complementary information related to the BT response during long treatment time to delimit the treatment conduct and contribute in the understanding of bio-physiological process associated with the anti-tumor mechanism of the drugs. 3.4 MNP. Pharmacokinetics (PK) by MR relaxation and MRI Nowadays, MNPs are applied for diagnosis, drug delivery and thermotherapy agents amongst others. MRI is a complementary technique to follow PK of MNP [10]. In Fig. 5 is represented the dependence of the ratio (I  − I )/I , proportional to i 0 0 MNP concentration. The measured image intensities I were normalized to the background I and the ratio (I   −  I )/I was calculated as a time function after 0 i 0 0 MNP injection. Two different areas of the liver were evaluated (red and blue Fig. 5 Dependence of the I /(I  − I ) ratio (proportional to the MNP concentration) as a function of time 0 i 0 after MNP injection. Two different areas of the liver were measured (red and blue lines) and, as a control, a muscle area was taken (line pink line) [10] 1 3 Kinetic studies of complex biomedical process by magnetic… lines) and one muscle area (pink line) was taken as control. The graphics have three regions with different slopes. The first one, which is associated with the entrance of the MNP in the liver: absorption period. The second one can be attrib- uted to the liver stationary state: residence. Finally, the last region is connected to the MNP excretion. From these measurements, it was possible to determine the principal MNP PK parameters as reported in Ref. [10]. A new metabolic route of MNP “in vivo” bio-distribution was described in base of this data. Nonetheless, the MNP MR “in vivo” studies are limited as con- sequence of the strength “negative contrast” introduced by MNP in T2 relaxation mechanism. It is necessary to make some complementary effort to overcome this restriction. 4 Conclusion “In vitro” and “in vivo” MR data gave unique complementary information related to the kinetic studies of complex biomedical processes. MR has contributed to the discovery of new pathways and drugs for treatment and to introduce modification in them. Furthermore, MR provides valuable information on bio-processes that occur over long periods of time, contributing to the understanding of the physi- ological processes and delimiting the treatment conduct. Nonetheless, the real quantitative separation of the different mobility’s (molec- ular and cellular), the metabolic activity, associated with the different pathologi- cal tissues regions still be an unsolved problem related to complex pathologies. This essential and complex MRI problem need many effort to be overcome. Nowadays, to obtain a real quantitative T1, T2, Diffusion and metabolic maps “in vivo”, in real time, is still a great challenge to the MR. Nevertheless, it is possible to attenuate, or some cases to avoid these restric- tions by having robust and standard protocols, decreasing the image time, by means of external and internal markers, employing adequate and well-character- ized phantoms and via the multi-parametric images among other procedures. In addition, adequate preparation for the technicians and medical experts working in MR is a success factor for achieving these proposes. Acknowledgements We are grateful to Lora Hospital, Santiago de Cuba and to the Medical-Surgi- cal-Research Center, Havana. Likewise, thanks to patients, volunteers and coworkers related to these studies. Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 Inter- national License (http://creat iveco mmons .org/licen ses/by/4.0/), which permits unrestricted use, distribu- tion, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made. References 1. A. Fernández, C. Cabal, J. Losada, E. Alvarez, C. Soler, J. Otero, Hemoglobin A 29, 181 (2005) 1 3 598 C. Cabal Mirabal et al. 2. M. Lores, C. Cabal, Appl. Magn. Reson. A 28, 1 (2005) 3. M. Lores, C. Cabal, O.R. Nascimento, A.M. Gennaro, Appl. Magn. Reson. 30, 121–128 (2006) 4. A. Fernandez, C. Cabal, M. Lores, J. Losada, E. Perez, Hemoglobin A 33, 206 (2009) 5. C. Cabal-Mirabal, E. González Dalmau, J. Berlanga Acosta, D. Darias Zayas, L. Herrera Mar- tínez, P. Lopez Saura, G. Guillén Nieto, J. Baldomero Hernández, C. González Delgado, L. Javier González, J. Radiol. Res. Pract. (2014). https ://doi.org/10.5171/2014.78398 0 6. C. Cabal-Mirabal, E. Gonzalez, L. Manuel Flores, J. Berlanga Acosta, L. Herrera Martinez, United State Patent Application Publication. US2016/0157750 (2016) 7. J. Berlanga Acosta, W. Savigne, C. Valdez, N. Franco, J. S. Alba, A. del Rio, P. Lopez-Saura, G. Guillen, E. Lopez, L. Herrera Martinez, J. Fernandez-Montequın, Int. Wound J. A 3, 232 (2006) 8. E. González Dalmau, C. Cabal-Mirabal, G. Sáurez Martínez, A. Lage Dávila, J. Ugarte Suarez, R. Cabanas Armada, G. Rodríguez Cruz, D. Darias Zayas, M. Rios Castillo, L. Valle Garrido, Pediatr. Int. (2014). https ://doi.org/10.1111/ped.12212 9. U. Bode, M. Massimino, F. Bach, M. Zimmermann, E. Khuhlaeva, M. Westphai, K. Fleischhack, Expert Opin. Biol. Ther. 12, 1649 (2012) 10. A. Ruiz, Y. Hernández, C. Cabal, E. González, S. Veintemillas-Verdaguer, E. Martinez, M.P. Morales, Nanoscale (2013). https ://doi.org/10.1039/c3nr0 1412f 1 3

Journal

Applied Magnetic ResonanceSpringer Journals

Published: Mar 26, 2018

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